Inhaler

ABSTRACT

The present disclosure relates to an inhaler component for producing a steam/air mixture or/and condensation aerosol in an intermittent and inhalation- or pull-synchronous manner, the inhaler component including: a housing; a chamber arranged in the housing; an air inlet opening for the supply of air from the surroundings to the chamber; an electrical heating element for evaporating a portion of a liquid material; and a wick having a capillary structure, which wick forms a composite structure with the heating element and automatically supplies the heating element with fresh liquid material after evaporation.

RELATED APPLICATIONS

This application is a division of application Ser. No. 14/296,803 filedJun. 5, 2014, which in turn is a continuation of U.S. patent applicationSer. No. 13/125,343, filed Apr. 21, 2011, now U.S. Pat. No. 8,833,364issued Sep. 16, 2014, which is a 35 U.S.C. § 371 National Phaseconversion of PCT/AT2009/000414, filed Oct. 21, 2009, which claimsbenefit of Austrian Application No. A 1660/2008, filed Oct. 23, 2008 andAustrian Application No. A 597/2009, filed Apr. 17, 2009, the contentsof which are incorporated in full herein by reference.

The invention relates to an inhalator component for the intermittentformation, synchronous with inhalation or drawing, of a vapor-airmixture or/and condensation aerosol, comprising: a housing; a chamberarranged in the housing; an air admission opening for the supply of airfrom the surroundings to the chamber; an electric heating element forevaporating a portion of a liquid material, wherein the vapor which isformed is mixed in the chamber with the air supplied through the airadmission opening, and the vapor-air mixture or/and condensation aerosolis formed; and a wick with a capillary structure, which wick forms acomposite with the heating element and automatically resupplies theheating element with the liquid material following evaporation.

The invention concerns inhalators which permit intermittent operationsynchronous with inhalation or drawing. An operating mode of this typeis present if the liquid material is heated and evaporated only duringdrawing or during inhalation. The heating element is largely deactivatedin intervals between two drawings or inhalations. The heating element isactivated or energized generally right at the beginning of drawing orinhalation, either manually, for example by means of a switch, butpreferably automatically via a suitable sensor and an electronicswitching circuit. In the latter case, inhalation—or drawing-activatedoperation of the inhalator is also referred to.

In the present patent application, the term “inhalator” refers tomedicinal and nonmedicinal inhalators. The term furthermore refers toinhalators for administering drugs and substances which are not declaredas drugs. The term also refers to smoking articles and cigarettereplacement articles, as contained, for example, in European patentclass A24F47/00B, in so far as said articles are intended to administerthe vapor-air mixture or/and condensation aerosol to the user. The term“inhalator” is also not intended to impose any restrictions on how thevapor-air mixture formed or/and condensation aerosol is supplied to theuser or to the user's body. The vapor-air mixture or/and condensationaerosol may be inhaled into the lungs or else also only supplied to themouth cavity—without inhalation into the lungs. Finally, the term“inhalator” includes both apparatuses which permit direct inhalationinto the lungs in a single step (“classic inhalators”) and apparatuseswhich—as in the case of a cigarette—require at least two steps, namelyfirst of all drawing into the mouth cavity (drawing volume: approx.20-80 mL) and—after putting the inhalator down—a following inhalationinto the lungs (“drawing inhalators”). In comparison to drawinginhalators, classic inhalators have a significantly higher airthroughput through the inhalator: approx. 100-750 mL/s in comparison to10-40 mL/s. By contrast, drawing inhalators generally have asignificantly higher flow resistance or drawing resistance than classicinhalators.

Definition of Terms:

Evaporation energy: sensitive plus latent quantity of heat which istransmitted to the liquid material actually evaporating.

Evaporative capacity: evaporation energy converted per unit of time.

Specific evaporative capacity: evaporative capacity related to the unitof mass of the evaporating liquid material.

Evaporator efficiency: quotient of the evaporation energy and energyproduced by the heating element.

Over the years, a multiplicity of inhalators and electric smokingarticles has been proposed, said inhalators and smoking articles usingelectric energy in order to evaporate drugs and/or aroma substances andproviding the vapor produced or/and the condensation aerosol formed to auser, optionally for inhalation.

GB 25,575 A.D.1911 (Elwin Kendal Hill) describes an inhalator with anelectric evaporator for evaporating medicaments. The apparatus consistsof a disk 38 and of a perforated covering 39. An absorption material 40absorbing the medicament and an electric heating element 41—for examplein the form of a resistance heating wire—are located in the spacebetween the disk 38 and the covering 39. The liquid medicament isautomatically supplied to the absorption material 40 and the heatingelement 41 from a supply container 30 via a corresponding number ofwicks 45. The air sucked up during inhalation flows through a conicalchannel 36, as a result of which the stream of air is focused at theevaporator and thereby absorbs the evaporated medicament. The evaporatordisk 38 is kept in position by means of spacer sleeves 44.

The particular disadvantages of said arrangement include the complicatedconstruction of the evaporator, the mounting thereof and the connectionof the wick to the evaporator. The multipart nature and complexstructure of said construction makes the inhalator expensive to produceand makes assembly complicated.

A serious disadvantage is that the ratio of the vapor outlet surface tothe evaporator volume is relatively small. This is firstly because ofthe specific geometry of the evaporator and is secondly caused by theabsorption material 40 and the electric heating element 41 beingsubstantially covered, specifically by the disk 38 and the covering 39.Said coverings are required by the construction in order to keep theabsorption material 40 and the electric heating element 41 together. Itis possible for the vapor formed in the interior of the evaporator toescape exclusively through the holes in the covering 39. As a result,even when the evaporative capacity in the evaporator is comparativelymoderate, a boiling crisis may occur, and therefore said arrangementappears unsuitable for intermittent operation synchronous withinhalation or drawing, said operation basically requiring a higherspecific evaporative capacity with simultaneously high evaporatorefficiency.

A further disadvantage is that, despite the precautions which have beentaken against the liquid medicament escaping from the supply container30, such an escape cannot be entirely prevented by the construction, inparticular if the supply container 30 is overfilled, for example due toerroneous operation. Finally, the fact that the liquid medicament in thesupply container 30 is virtually freely exposed to the ambient air,which may lead to oxidation of the medicament or/and to a change in thecomposition thereof due to vaporization effects, should be viewedcritically.

U.S. Pat. No. 2,057,353 (Clinton L. Whittemore) describes an evaporatorunit for a therapeutic apparatus, consisting of a vessel A for receivinga liquid medicament x, electric conductors 1 and 2 protruding into thevessel through the vessel base, a heating wire 3 which is connected tothe electric conductors, and a wick D around which the heating wire 3 iscoiled and which extends from said heating wire to the vessel base. Thevessel has an air admission opening 4 and a vapor outlet opening 5 whichare both curved inward in order to avoid the medicament escaping fromthe vessel.

A disadvantage of this construction is the complicated process ofproducing the connection between the heating element and the wick. Theheating wire has to be coiled around the wick prior to the composite.Said procedure proves complicated in particular because the parts whichare to be joined together are customarily of extremely small dimensions.In addition, it is difficult to ensure that the heating wire coils allbear against the wick. Local detachment may result in the heating wireoverheating in these regions, and the resistance material can age morerapidly. This problem also relates to the regions where the heating wireis connected to the electric conductors 1 and 2.

A further disadvantage involves the outer surface of the wick D beingpartially covered by the heating element 3 being coiled therearound. Inthis respect, the coiling constitutes an obstacle to the vapor emergingfrom the wick. Said obstruction of the flow of vapor may entail similarconsequences as have already been described in more detail in thedocument GB 25,575 A.D.1911. Moreover, the vapor formed, as it flowsout, comes at least partially into contact with the hot heating wire,which may result in thermal decomposition of the medicament X.

Another disadvantage is that the wick D is held in position merely bythe relatively thin heating wire 3. Even a vibration could change theposition of the wick D and could considerably change the flow and mixingratios between the air sucked in through the opening 4 and the vaporflowing out from the wick D and have an adverse effect on the aerosolformation. The apparatus can be operated only in an upright or slightlyinclined position; despite the structural measures taken, it is notpossible to entirely prevent the medicament x from escaping from thevessel A. Finally, the medicament x in the vessel A is virtually freelyexposed to the ambient air; a fact which also has to be considered asbeing highly unfavorable.

FR 960,469 (M. Eugene Vacheron) describes an inhalation apparatus withan electric evaporator. The inhalation apparatus comprises an electricheating cartridge 4, 5, 6 and a wick 16, which wick is impregnated withthe liquid stored in the container 1. The heating cartridge is locatedoutside the container 1, i.e. is not connected directly to the wick. Thespecial structural conditions make the inhalation apparatus sluggish interms of heating and the latter appears suitable at most for continuousoperation of the evaporator; intermittent operation synchronous withinhalation or drawing does not appear to be able to be realized.

CA 2,309,376 (Matsuyama Futoshi) describes an evaporator or atomizer formedicinal applications, consisting of (FIGS. 3A-3C) a vessel 1containing a liquid composition and a rod-shaped, porous material 3which is installed in the vessel 1. The rod-shaped, porous material 3dips at one end into the liquid composition while the other end extendsfreely upward outside the vessel 1. The vessel 1 and the rod-shaped,porous material 3 are arranged in a curved container 5. The curvedcontainer 5 firstly keeps the vessel in position and secondly containsan electric heating device 6 which encases an upper end section of therod-shaped, porous material 3 at a distance, the distance preferablybeing within the range of 0.8-2.5 mm. The capillary forces in therod-shaped, porous material 3 cause the liquid composition to be suckedupward where the composition is finally evaporated by the electricheating device 6. In this case, the active compounds contained in theliquid composition are atomized and pass out of the curved container 5through the opening 9 into the space such that they can be inhaled bythe user. The liquid composition consists of an aqueous solution inwhich an active compound concentrate is dissolved or dispersed. Theaqueous solution preferably consists of water or of a mixture of waterand ethanol. The active compound concentrate is obtained from the leavesof Lagerstroemia Speciosa, and contains up to 15% by mass of corosolicacid. The active compound concentrate supposedly acts in a mannerreducing blood sugar. The portion of active compound concentrate(calculated in the form of corosolic acid) in the aqueous solution is0.5-3.0% by mass.

The evaporator is designed for continuous operation. The electricheating device 6 is arranged at a distance from the porous material 3and consequently does not form a composite therewith. The gap in betweenconstitutes a high resistance to heat conduction. Intermittent operationwith a correspondingly high specific evaporative capacity would berealized only if the heat were transmitted by means of heat radiation.For this purpose, the electric heating device 6 would need to be heatedup suddenly to a very high temperature. The liquid composition wouldprimarily evaporate in the border zone facing the heating device andwould flow through the gap already mentioned into the surroundings.Irrespective of the implementation of said concept in practice, thevapor formed would in any case come into contact with the glowingsurface of the heating device 6, as a result of which the activecompound concentrate would be at least partially thermally decomposed.

U.S. Pat. No. 6,155,268 (Manabu Takeuchi) describes an aroma-generatingapparatus consisting of (FIG. 1A) a chamber 121 with an air admission 18and a mouthpiece opening 22 and mouthpiece 16, thus forming a gaspassage channel 20, and furthermore comprises a liquid container 32 forreceiving a liquid aroma substance 34, and finally a capillary tube 36with a first end section which dips into the liquid in the container 32,and with a second end section which communicates with the gas passagechannel 20, and furthermore comprises a heating element 42. The liquidaroma substance 34 flows by means of the capillary forces acting in thecapillary tube 36 to the heating element 42 where said substance isevaporated and flows as a stream of vapor out of the opening 36 b intothe gas passage channel 20. The stream of air entering from the outsideinto the chamber 121 through the air admission 18 is focused by theapertured diaphragm 24, 24 a at the capillary opening 36 b, as a resultof which favorable conditions for intimate mixing between the vapor andsucked-up air and for the formation of an aerosol are intended to beprovided.

In alternative embodiments (FIGS. 8-13), plate-like heating elements areproposed. In further exemplary embodiments (FIGS. 14 and 15), theinterior of the capillary tube is filled with a pore structure 302which, in one variant embodiment, can also protrude out of the capillarytube, wherein, in said latter case, the heating element 425 can bearranged at the end of the protruding pore structure.

The disadvantage again of said arrangements is the relativelycomplicated construction of the evaporator unit—in this case consistingof the capillary tube and the heating element. Said two microcomponentshave to be connected to each other, and the heating element has to beconnected to the electric supply, which, in the specific case, canprobably be realized only via electric wires. Unfortunately, thisdocument does not provide more precise instructions in this regard.

For the arrangements according to FIGS. 14 and 15, the same applies ashas already been explained with regard to GB 25,575 A.D.1911: the ratioof the vapor outlet surface to the evaporator volume is extremely small.This is because the pore structure 302 is substantially covered by theencasing 301 and the heating element 425. As a result, even at amoderate evaporative capacity, a boiling crisis may occur, and thereforethe functioning of said arrangements should basically be doubted,particularly if intermittent operation synchronous with inhalation ordrawing is required.

Two variant embodiments are proposed for the liquid container 32: in afirst variant embodiment (FIG. 1A), the liquid container is a specifiedpart of the aroma-generating apparatus. The liquid container can berefilled via a filling opening. However, such a refilling involves risksfor the environment, in particular if the liquid aroma substancecontains drugs or poisons, such as, for example, nicotine, and therefilling is carried out by the user him/herself. In an alternativevariant embodiment (FIG. 8), the liquid container is designed as a smallinterchangeable container. Details regarding the coupling up of saidcontainer have not been disclosed. Small interchangeable containersalways involve the risk of being swallowed by small children, which mayhave a potentially lethal outcome, in particular if the liquid aromasubstance contains drugs or poisons, such as, for example, nicotine.

The arrangement according to FIG. 8 furthermore shows an exchangeablemouthpiece 161 with a hollow-cylindrical extension which lines a largepart of the chamber 121 and extends virtually as far as the mouth of thecapillaries 371. Condensate residues arising in the chamber 121accumulate primarily on the inner surface of the hollow-cylindricalextension and can be removed together with the mouthpiece. A problem isthat the inner surface is capable only to a limited extent of receivingcondensate. In particular if the liquid aroma substance containsrelatively large portions of low-boiling fractions with a high vaporpressure—for example ethanol or/and water, the mouthpiece has to beexchanged within short intervals. Also, drops are formed on the innersurface of the mouthpiece under the influence of surface tensions, thedrops steadily increasing in volume until the adhesion forces areultimately no longer sufficient in order to hold the drops, and thelatter combine to form relatively large accumulations of liquid. Saidaccumulations of liquid may have an adverse effect on the functioning ofthe apparatus but may also constitute a risk for the user and theenvironment if said accumulations contain drug residues or poisons, suchas, for example, nicotine. However, even the option of the userhim/herself being able to remove the condensate from the apparatusinvolves a risk for the environment.

U.S. Pat. Nos. 4,922,901, 4,947,874 and 4,947,875 (Johny L. Brooks etal.) describe articles for releasing and administering drugs or/andaromas using an exchangeable unit 12 which contains an electricresistance heating element 18, the surface of which is larger than atleast 1 mA2/g; the electric resistance heating element 18 carriesaerosol-forming substances. The electric resistance heating element 18preferably consists of a porous or fibrous material—for example carbonfibers, which material is impregnated with a liquid aerosol former. Thearticles furthermore contain a drawing-activated electronic control unit14 for controlling the stream through the electric resistance heatingelement 18 and are capable of administering at least 0.8 mg of aerosolor drug per drawing, with at least 10 drawings being possible in totalbefore the exchangeable unit 12 together with the resistance heatingelement 18 has to be replaced by a new one.

In this article, the entire liquid material to be evaporated istherefore already pre-stored in the resistance heating element 18. Asupply of liquid via a wick is not provided. This also results in thefollowing disadvantages: the aerosol-forming substances or the drugor/and any added aroma substances which are released, for example,during the final drawing have already been repeatedly heated upbeforehand, which circumstance prompts thermal decomposition of theaerosol-forming substances. In addition, said preceding heatingoperations are unfavorable in so far as additional electric energy isrequired for this purpose, said energy not making any contribution tothe actual evaporation and aerosol formation. This results in a very lowevaporator efficiency. A further disadvantage is that, in the case ofmixtures of various aerosol-forming substances, drugs and aromasubstances, with different boiling points of the individual substances,the chemical composition of the aerosol formed and the organoleptic andpharmacological effect thereof varies from one inhalation to the next,with low-boiling fractions increasingly being evaporated during thefirst drawings, and higher boiling substances increasingly beingreleased during the final drawings. Finally, the exchangeable unit 12which is relatively complicated to produce, and therefore also theheating element 18, has to be replaced after just approximately 10drawings, which makes the use of said articles expensive.

U.S. Pat. Nos. 5,060,671 and 5,095,921 (Mary E. Counts, D. Bruce Loseeet al.) describe an article 30 (FIG. 4) in which an aroma-releasingmedium 111 is heated by electric heating elements 110 in order toprovide inhalable aromas in vapor or aerosol form. The article containsa plurality of charges of the aroma-releasing medium 111, which chargesare heated sequentially and thereby provide individual drawings. Theplurality of charges of aroma-releasing medium 111 are applied to theheating elements 110 preferably in the form of a covering, coating or athin film and may also contain aerosol-forming substances. The adhesionof the aroma-releasing medium 111 to the heating elements 110 can beimproved by an adhesion-promoting agent, for example pectin. Theelectric heating elements 110 and the charges of aroma-releasing medium111 applied to said heating elements are preferably arranged in anexchangeable unit 11 which is connected to a reusable unit 31 viaelectric contact pins. The reusable unit 31 contains an electric energysource 121 and an electronic control circuit 32. U.S. Pat. No. 5,322,075(Seetharama C. Deevi et al.) describes a similar article.

Although said article eliminates some of the disadvantages of thepreviously described articles (U.S. Pat. Nos. 4,922,901, 4,947,874 and4,947,875), the construction of the exchangeable unit 11 appears to beeven more complex, since, in the specific case, a multiplicity ofheating elements is provided together with electric contact connectionmeans. If it is furthermore taken into consideration that the complex,exchangeable unit 11 scarcely permits more than 15 drawings (cf. FIGS.7A-7K), it is clear that the use of such an article would be expensive.Furthermore, in the specific case, the aroma-releasing medium 111 ispresent in the form of a relatively large thin layer which, particularlyduring storage of the exchangeable unit 11, is exposed to diverseenvironmental influences (oxidation, etc.). In order to avoid saidinfluences, a complicated packaging which protects the medium 111 fromthe environment but does not as far as possible touch the medium wouldhave to be provided. U.S. Pat. Nos. 5,060,671 and 5,095,921 do notdiscuss this aspect.

US 2005/0268911 (Steven D. Cross et al.) is very similar to thepreviously described article according to U.S. Pat. Nos. 5,060,671 and5,095,921 and describes an apparatus for producing and dispensing aplurality of doses of a condensation aerosol for the inhalation of highpurity medicaments and, in the simplest case (FIG. 1A), consists of anair duct 10 with an inlet and an outlet, a plurality of supports 28which are arranged in the air duct and each bear a certain dose of asubstance/medicament, and a device for evaporating said discrete doses.The stream of air flowing in through the inlet is conducted to thesupports 28 where the condensation aerosol is finally formed. Thesupports 28 each contain an electric resistance heatingelement—preferably consisting of a metal foil 78 of stainless steel. Themetal foil heating elements 78 are preferably mounted on a printedcircuit board (FIG. 4). The disadvantages of the article according toU.S. Pat. Nos. 5,060,671 and 5,095,921 apply equally to the apparatusaccording to US 2005/0268911.

U.S. Pat. Nos. 5,505,214 and 5,865,185 (Alfred L. Collins et al.)describe electric smoking articles consisting of (FIG. 4; U.S. Pat. No.5,505,214) an exchangeable unit 21 and a reusable part 20. Theexchangeable unit 21 contains tobacco aromas 27 which are located on asupport 36. The reusable part 20 contains a plurality of heatingelements 23 which are supplied with current or energy by an electricenergy source—for example a rechargeable battery—via an electric controlcircuit. After the exchangeable unit 21 is inserted into the reusablepart 20, the support 36 comes to lie on the heating elements 23. Duringinhalation or drawing, one individual heating element is activated ineach case by the control circuit, as a result of which the support 36 ispartially heated and the tobacco aromas 27 are evaporated and released,optionally in the form of an aerosol. In the exemplary embodimentaccording to FIG. 4, the reusable part 20 has eight heating elements 23,with eight inhalations or drawings being possible similarly to acigarette. The exchangeable unit 21 then has to be replaced by a newunit.

The smoking articles according to U.S. Pat. Nos. 5,505,214 and 5,865,185have the advantage over the article according to U.S. Pat. Nos.5,060,671 and 5,095,921 that the heating elements 23 are arranged in astationary manner in the reusable part 20 and can therefore be used morethan once. Electric contacts between the exchangeable unit 21 and thereusable part 20 are not required. However, a disadvantage over thearticle according to U.S. Pat. Nos. 5,060,671 and 5,095,921 is that thesupport 36 has to be heated in addition to the heating elements 23; theheat required for this lowers the evaporator efficiency. The otherdisadvantages, already explained earlier, of the article according toU.S. Pat. Nos. 5,060,671 and 5,095,921 are accordingly applicable.

U.S. Pat. No. 4,735,217 (Donald L. Gerth et al.) describes a meteringunit for administering evaporated medicaments in the form of fineaerosol particles which pass into the lungs by inhalation. In oneexemplary embodiment (FIGS. 4 and 5), the metering unit consists of afilm-like NICHROME ® heating element segment 72 (length×width×thickness:1×⅛.times.0.001 inch) which is connected in series to a battery 65 and aswitch 60, 69 activated by a stream of air or by drawing. The medicamentto be evaporated—for example nicotine—is present in the form of a solidpellet 40 which makes contact with the heating element 72. As analternative, the medicament to be evaporated can be applied directly tothe heating element surface in the form of a coating or a film.

Some of the disadvantages of this metering unit have already beenmentioned in U.S. Pat. No. 4,922,901. Added thereto is the fact that thetransfer of heat from the heating element to the pellet turns out to behighly unfavorable. A large part of the heating element 72 is heated upwithout a purpose, since only a small part of the heat formed inperipheral regions of the heating element can be used for the pellet. Inprinciple, it is disadvantageous that, in order to form the pellet, useis made of solids which generally have to be melted first before theycan be evaporated, thus causing a further deterioration in the energybalance.

EP 1,736,065 (Hon Lik) describes an “electronic cigarette” for atomizinga solution of nicotine and essentially consists of a container 11 forreceiving the liquid to be atomized, and an atomizer 9. An atomizerchamber 10 formed by the atomizer chamber wall 25 is located in theinterior of the atomizer 9. An electric heating element 26, for examplein the form of a resistance heating wire or a PTC ceramic, is arrangedwithin the atomizer chamber 10. Furthermore, ejection holes 24, 30pointing in the direction of the heating element 26 are provided in theatomizer or in the atomizer wall 25. The container 11 contains a porousbody 28—for example composed of synthetic fibers or foam, which isimpregnated with the liquid to be atomized. The atomizer chamber wall 25is likewise surrounded by a porous body 27—for example consisting ofnickel foam or of a metal felt. The porous body 27 is in contact withthe porous body 28 via a bulge 36. Capillary forces have the effect thatthe porous body 27, which at the same time forms the outer casing of theatomizer 9, is infiltrated by the liquid to be atomized. The atomizerfurthermore comprises a piezoelectric element 23.

The “electronic cigarette” is operated in a manner activated by drawing.During drawing, a negative pressure arises in the atomizer chamber 10,since the latter is connected to the mouthpiece 15. As a result, airflows out of the surroundings via the ejection holes 24, 30 into theatomizer chamber. The high flow velocity in the ejection holes 24, 30has the effect that liquid is sucked out of the porous body 27 and isentrained by the stream of air in the form of drops (Venturi effect).The nicotine-containing liquid passes into the atomizer chamber 10 wherethe liquid is atomized by ultrasound by means of the piezoelectricelement 23. The heating element 26 is intended to bring about additionalatomization or evaporation of the solution of nicotine. In analternative variant embodiment, the atomization takes place exclusivelyby means of the heating element 26.

The arrangement has functional similarities to the smoking apparatusdisclosed in U.S. Pat. No. 4,848,374 (Brian C. Chard et al.). It isdisadvantageous in both cases that, similarly as with a cigarette, themetering of the liquid to be atomized and of the aerosol formed dependson the particular drawing profile of the user. However, this isundesirable for medicinal or therapeutic applications. Added to this isthe fact that the atomization by means of ultrasound generally producessignificantly larger aerosol particles than condensation aerosolscustomarily have. Said larger particle fractions do not pass into thepulmonary alveoli but rather are already absorbed in lung sectionslocated upstream, which, in the case of drugs acting systemically, suchas nicotine, has a highly unfavorable effect on the absorption kineticsand the efficiency of supply of the active compound. Furthermore, inparticular in the case of the alternative variant embodiment withoutultrasound atomization, it has to be doubted whether the electricheating element, which is designed in a manner similar to anincandescent bulb wire, is even capable of transmitting the heatingenergy required during drawing for the evaporation to the liquidmaterial. This would probably be possible only by heat radiation, forwhich purpose the heating element would have to be brought proverbiallyto a glowing temperature. Such high temperatures are basicallyassociated with various risks and disadvantages—including with the riskof thermal decomposition of the liquid to be atomized or alreadyatomized. Finally, it should be considered to be a high safety risk thatthe container containing the highly poisonous solution of nicotine isopen on an end side and furthermore can be detached from the “electriccigarette”. This risk has already been identified, and in adevelopment—as in DE 202006013439U—has been partially neutralized by thecontainer being formed by a hermetically sealed cartridge, but thecartridge can disadvantageously still always be detached from the“electric cigarette” and can be swallowed, for example by smallchildren.

Finally, it should be noted that some of the documents just depictedhave been described, although they are not included in the generic typeof the invention referred to at the beginning, since they at leastdepict the further prior art and in this respect are worthy of beingtaken into consideration.

The invention is based on the object of eliminating the disadvantagesshown above of the arrangements known from the prior art. The inventionis based in particular on the object of designing an inhalator componentof the type described at the beginning such that the high specificevaporative capacity required for intermittent operation synchronouswith inhalation or drawing can be realized with simultaneously highevaporator efficiency. The power and energy requirement required shouldbe able to be covered here by an energy store approximately in theformat of an average cell phone battery. The occurrence of a boilingcrisis in the wick is intended to be avoided, and the liquid material isintended to be able to be evaporated as gently as possible, i.e. withoutsubstantial thermal decomposition.

The inhalator component is furthermore intended to permit user-friendlyand safe operation, and is intended to be able to be produced ascost-effectively as possible, which specifically means: the composite isintended to be infiltrated as rapidly as possible by the liquid materialsuch that substantial waiting times do not have to be maintained betweentwo inhalations or drawings. The inhalator component is intended to beable to be operated independently of position. The risk of liquidmaterial—including liquid condensate residues—passing into theenvironment or impairing the functioning of the inhalator component isintended to be minimized. The composite is intended to be able to beproduced as cost-effectively as possible. The inhalator component isintended to be configured to be handy and ergonomic and to be simple tooperate.

Furthermore, the properties of the vapor-air mixture formed or/andcondensation aerosol are intended to be able to be influenced at leastwithin certain limits—in particular the particle size distribution ofthe condensation aerosol formed and the organoleptic effects thereofFinally, the inhalator component is intended to be designed in twobasically different variant embodiments such that it can be used both inclassic inhalators and in drawing inhalators.

The object is achieved in that the composite is of planar design, and atleast one heated section of the composite is arranged in the chamber ina contact-free manner, and the capillary structure of the wick in saidsection is substantially exposed at least on one side of the planarcomposite. In a development of the invention, the capillary structure ofthe wick in said section is substantially exposed on both sides of theplanar composite. Owing to the fact that the capillary structure of thewick in said section is substantially exposed, the vapor formed can flowunhindered out of the wick, as a result of which the evaporativecapacity can be increased and a boiling crisis in the wick can beavoided.

Explanations of Terms:

“Planar composite” means that the heating element and the wick arearranged in the same surface or/and in mutually parallel surfaces andare connected to each other, the same surface or/and the mutuallyparallel surfaces comprising at least one planar surface or area, atleast one curved surface or area, or a combination of at least oneplanar surface or area and at least one curved surface or area. Thecapillary transport of the liquid material in the planar composite takesplace primarily in the surface direction. “In a contact-free manner”means that neither the chamber wall nor other structural elements of theinhalator component are touched; the effect achieved by the contact-freearrangement in the chamber is that the heat conduction losses of thecomposite are substantially reduced in said section, and the compositeis heated until the liquid material stored in the wick can evaporate.

“Chamber” is intended also to include channels; therefore, even atubular channel is included in the term “chamber”; in this case, an opentube end could form, for example, the air admission opening.

In a preferred refinement, the planar composite has a thickness of lessthan 0.6 mm, and, in a particularly preferred refinement, a thickness ofless than 0.3 mm. The result of this dimensioning is that the heat whichis introduced in a planar manner can flow in efficiently by means ofheat conduction—i.e. at a low temperature gradient, to the exposed wicksurface or capillary structure where said heat causes the evaporation ofthe liquid material. In addition, vapor already formed in the interiorof the wick can more easily reach the exposed wick surface. Theseconditions permit a further increase in the evaporative capacity andcontribute to the liquid material being evaporated particularly gently.It should be noted that this does not merely involve simple dimensioningbut rather an essential feature of the invention. Even the inventor wassurprised to find in experiments that planar wicks with an exposed wicksurface and a thickness <300 μm still exhibit a wicking effect in thesurface direction.

It is considered as being according to the invention that the compositeis designed in the form of a plate, film, strip or band. Said planararrangements make it possible to use production methods permittingparticularly economic mass production.

According to the invention, the planar composite contains one of thefollowing structures: a fabric, open-pored fiber structure, open-poredsintered structure, open-pored foam or open-pored deposition structure.Said structures are suitable in particular for providing a wick bodywith a high degree of porosity. A high degree of porosity ensures thatthe heat produced by the heating element is used for the most part forevaporating the liquid material located in the pores, and highevaporator efficiency can be obtained. Specifically, a porosity ofgreater than 50% can be realized with said structures. The open-poredfiber structure can consist, for example, of a nonwoven fabric which canbe arbitrarily compacted, and can additionally be sintered in order toimprove the cohesion. The open-pored sintered structure can consist, forexample, of a granular, fibrous or flocculent sintered compositeproduced by a film casting process. The open-pored deposition structurecan be produced, for example, by a CVD process, PVD process or by flamespraying. Open-pored foams are in principle commercially available andare also obtainable in a thin, fine-pored design.

In one variant embodiment of the invention, the planar composite has atleast two layers, wherein the layers contain at least one of thefollowing structures: a plate, foil, paper, fabric, open-pored fiberstructure, open-pored sintered structure, open-pored foam or open-poreddeposition structure. In this case, certain layers can be assigned tothe heating element, and other layers to the wick. For example, theheating element can be formed by an electric heating resistor consistingof a metal foil. However, it is also possible for one layer to take onboth heating element and wick functions; such a layer may consist of ametal wire fabric which, firstly, because of the electric resistancethereof, makes a contribution to the heating, and, secondly, exerts acapillary effect on the liquid material. The individual layers areadvantageously but not necessarily connected to one another by a heattreatment, such as sintering or welding. For example, the composite canbe designed as a sintered composite consisting of a stainless steel foiland one or more layers of a stainless steel wire fabric (material, forexample AISI 304 or AISI 316). Instead of stainless steel, use may alsobe made, by way of example, of heating conductor alloys—in particularNiCr alloys and CrFeAl alloys (“KANTHAL®”) which have an even higherspecific electric resistance than stainless steel. The materialconnection between the layers is obtained by the heat treatment, as aresult of which the layers maintain contact with one another—even underadverse conditions, for example during heating by the heating elementand resultantly induced thermal expansions. If the contact between thelayers is lost, a gap could form which, firstly, could interfere withthe coupling in terms of capillary action and, secondly, thetransmission of heat from the heating element to the liquid material.

In an analogous refinement of the invention, it is provided that thecomposite is of linear design, and at least one heated section of thecomposite is arranged in the chamber in a contact-free manner, and thecapillary structure of the wick in said section is substantiallyexposed. Owing to the fact that the capillary structure of the wick insaid section is exposed, the vapor formed can flow unhindered out of thewick, thus enabling the evaporative capacity to be increased and aboiling crisis in the wick to be avoided. The liquid material istransported in terms of capillary action in the linear compositeprimarily in the longitudinal direction of the linear composite. Theterms “in a contact-free manner” and “chamber” have already beenexplained earlier.

The linear composite preferably has a thickness of less than 1.0 mm,wherein the thickness is defined by: √{square root over (4*A/π)} (Arefers to the cross-sectional area of the composite). This dimensioninghas the result that the heat introduced linearly can flow efficiently bymeans of heat conduction—i.e. at a low temperature gradient—to theexposed wick surface where it causes evaporation of the liquid material.In addition, vapor already formed in the interior of the wick can moreeasily reach the exposed wick surface. These conditions permit a furtherincrease in the evaporative capacity.

According to the invention, the linear composite contains at least oneof the following structures: wire, yarn, an open-pored sinteredstructure, open-pored foam or open-pored deposition structure. Saidstructures are suitable in particular for providing a linear compositewith sufficient mechanical stability and a high degree of porosity.

In a preferred refinement of the planar or linear composite, the heatingelement is at least partially integrated in the wick. This arrangementhas the advantageous effect that the heat is produced and releaseddirectly in the wick body and is transmitted there directly to theliquid material to be evaporated. The heating element can consist, forexample, of an electrically conductive thin layer of platinum, nickel,molybdenum, tungsten or tantalum, said thin layer being applied to thewick surface by a PVD or CVD process. In this case, the wick consists ofan electrically non-conductive material—for example of quartz glass. Ina simpler refinement of the invention in terms of production, the wickitself at least partially consists of an electric resistance material,for example of carbon, of an electrically conductive or semi-conductiveceramic or of a PTC material. It is particularly favorable if theelectric resistance material is metallic. Metals have greater ductilitythan the previously mentioned materials. This property has provenadvantageous in so far as the composite is exposed during operation to athermal alternating load, thus causing the induction of thermalexpansions. Metals can better compensate for such thermal expansions.Furthermore, metals have a higher impact toughness by comparison. Thisproperty has proven an advantage whenever the inhalator component isexposed to impacts. Examples of suitable metallic resistance materialsinclude: stainless steels, such as AISI 304 or AISI 316, and heatingconductor alloys—in particular NiCr alloys and CrFeAl alloys(“KANTHAL®”), such as DIN material number 2,4658, 2,4867, 2,4869,2,4872, 1,4843, 1,4860, 1,4725, 1,4765 and 1,4767.

In a further preferred refinement of the planar or linear composite, itis provided that the connection between the heating element and the wickextends over the entire extent of the wick. In this case, it isinsignificant whether the heating element is also used as such, i.e. isheated, over the entire extent thereof, or only partially. This dependson the particular position of the electric contact connection of theheating element. Even if said contact connection takes place at theouter ends of the heating element, the heating element does notinevitably have to contribute over the entire extent thereof toevaporating the liquid material. Sections of the heating element canthus touch structural components which substantially dissipate the heatproduced in the heating element, and therefore the liquid material inthe wick is virtually not heated at least in said section. However, saidoutflowing heat would be considered in the energy balance as a loss.This refinement makes it possible to use production processes whichprovide significant cost advantages over the prior art and for the firsttime make mass production economical. The planar composite can thus beobtained by large scale manufacture from a planar multiple panel by thecomposite being detached from said multiple panel by means of suitableseparating processes, such as punching or laser cutting. The linearcomposite can advantageously be obtained from an endless material. Theterm “endless material” also includes a material having a finite lengthif said length is much larger than the length of the linear composite.

As has already been explained earlier, a high degree of porosity of thewick and of the composite is desirable with regard to effective use ofthe heat energy introduced by the heating element. The porosity canadditionally be increased by the composite or the preliminary productionstage thereof—for example the multiple panel—being etched. By way ofexample, a sintered composite consisting of a stainless steel foil andone or more layers of a stainless steel mesh (for example AISI 304, AISI316) can be correspondingly treated in an aqueous etching bathconsisting of 50% of azotic acid and 13% of hydrofluoric acid, whereinthe electric resistance of the heating element and/or composite can alsobe influenced, namely increased, as a side effect.

According to the invention, the surface of the composite or thepreliminary production stage thereof can also be activated. This measurealso includes cleaning of the surface and brings about better wetting ofthe composite material by the liquid material and, associated therewith,more rapid infiltration of the wick. For example, for the sinteredcomposite cited previously by way of example and consisting of astainless steel foil and one or more layers of a stainless steel mesh,treatment in 20% strength phosphoric acid is very readily suitable inorder to obtain the previously mentioned effects.

In an advantageous refinement of the invention, the wick is designed asarterial wick. Said type of wick is used in particular in heat exchangertubes and is described more precisely in the relevant literature—see,for example, ISBN 0080419038. A wick of this type can consist, forexample, of a bundle of channels or capillaries—“arteries” which aresurrounded by a finer pore structure or are formed by the latter. Incomparison to a homogeneous pore structure of identical capillary actionor identical capillary pressure (capillary rise), the bundle of channelsor capillaries offers a lower flow resistance to the liquid material,thus enabling the infiltration of the wick with the liquid material tobe substantially accelerated.

In one variant embodiment, the wick is perforated in the thicknessdirection. The perforation can take place, for example, by means oflaser and has the following effects: firstly, the porosity is furtherincreased; secondly, the flow resistance in the thickness direction isreduced. The latter effect occurs in particular when an arterial wick isused in so far as the liquid material in the wick undergoes an increasein pressure during the evaporation, and the perforation acts as pressurerelief. This avoids the vapor formed in the wick from pressing theliquid material back via the arteries to the source of the liquidmaterial, which can severely disturb the supply of liquid material.

It is furthermore considered as being according to the invention thatthe planer composite is of substantially flat design, and the airadmission opening is designed as a slot-shaped channel, and theslot-shaped channel is oriented parallel to the flat composite surface.Analogously, it is considered as being according to the invention thatthe linear composite is of substantially rectilinear design, and the airadmission opening is designed as a slot-shaped channel, and theslot-shaped channel is oriented parallel to the rectilinear composite.By means of these geometrically simple arrangements, very favorablemixing conditions between the inflowing air and the vapor emerging fromthe wick can be provided, which mixing conditions can furthermore bevaried in a simple manner by changing the position of the slot-shapedchannel or/and by changing the slot height; it is thereby possible tohave a certain influence on the properties of the aerosol formed—inparticular on the size of the aerosol particles formed.

According to the invention, the composite passes through the chamber inthe manner of a bridge and is mounted by two end sections on twoelectrically conductive, plate-like contacts, and the heating element isin contact electrically with the contacts. If it is considered that thecomposite involves an extremely small and mechanically sensitivecomponent which, in addition, is exposed to the flow forces of the airflowing into the chamber and to forces as a consequence of thermalexpansion, it is clear that the arrangement just described is arelatively stable and simple to produce anchoring and contact connectionof the composite. In a preferred refinement of the invention, theelectric contact connection of the heating element consists of a weldedor sintered connection. The welded connection can be produced by spotwelding, resistance welding, ultrasound welding, laser welding, bondingor other suitable welding processes. It is particularly favorable forthe welding or sintering if the plate-like contacts consist of the sameor of a similar material as the heating element. In another advantageousrefinement of the invention, the electric contact connection of theheating element consists of an adhesive bonding connection by means ofan electrically conductive adhesive, for example by means of asilver-containing adhesive on the basis of epoxide. In this case, theplate-like contacts can in principle be produced from any electriccontact material as long as the material is compatible with the adhesiveused; as an alternative, the plate-like contacts can also be formed byprinted circuit boards or by a common printed circuit board. Thickcopper printed circuit boards having copper layer thicknesses in therange of 100-500 μm are preferred because of the better heatdissipation. Of course, the invention is not restricted to thepreviously mentioned contact connection processes. As an alternative,the electric contact connection could also take place by means ofmechanical clamping. In a development of the invention, the plate-likecontacts protrude out of the outer surface of the housing in the form oftwo plug contacts. The two plug contacts are provided in order to supplythe required electric energy to the heating element.

In a preferred development of the invention, one end of the compositeprojects into a capillary gap, the flow resistance of which is lowerthan the flow resistance of the wick. The capillary gap feeds the wickwith liquid material; the flow resistance which is reduced in comparisonto the wick causes the liquid material to pass more rapidly to theevaporation zone in the composite. As a result, however, the timerequired to completely infiltrate the wick again with liquid materialfollowing evaporation is also reduced. This time corresponds to awaiting time which should be at least maintained between two drawings orinhalations. If said waiting time is not maintained, this may result ina reduction in the emitted quantity of vapor or drug dose. In addition,due to the composite being heated up in some sections without liquidmaterial, local overheating causing damage to the composite orshortening the service life thereof may occur. In a development of theinvention, it is provided that the cross section of the capillary gap isgreater than the cross section of the composite. This has the effectthat the liquid material partially circumvents the wick in the manner ofa bypass and thereby passes even more rapidly to the evaporation zone inthe composite. In a preferred refinement of the invention, the heatingelement of the composite is in contact connection electrically in thecapillary gap. This results in a highly space-saving arrangement.

A preferred embodiment of the invention relates to an inhalatorcomponent with a liquid container which is arranged in the housing or isconnected to the housing and contains the liquid material, together withan openable closure; according to the invention, the liquid containercan neither be removed from the housing nor separated from the housing,and the liquid material in the liquid container can be coupled in termsof capillary action to the capillary gap by manual opening of theopenable closure. The liquid container can therefore not be removed fromthe inhalator component by the user, even if the liquid material is usedup, which can be considered to be an advantage in terms of safety inparticular if the container contains drugs or/and poisons, for example,nicotine. The housing of the inhalator component is too large to beswallowed by small children. Refilling of the liquid container is notprovided; on the contrary, the inhalator component together with theliquid container forms a disposable article which should be disposed ofproperly after the liquid material is used up. The liquid material isstored in the liquid container in a hermetically sealed manner. Accessof air or UV rays is very substantially prevented. In addition, theliquid container can contain an inert gas, such as argon, nitrogen orcarbon dioxide, which additionally protects the liquid material fromoxidation. The openable closure of the liquid container is expedientlyopened only shortly prior to use of the inhalator component, after whichthe liquid material passes via the capillary gap to the wick andinfiltrates the latter. The openable closure is opened in a simplemanner manually without the assistance of special aids.

In a first variant embodiment, the liquid container is connected rigidlyand permanently to the housing or itself forms part of the housing. Theliquid container may be designed, for example, as a separate part whichis connected nonseparably to the housing by an adhesive bondingconnection or a welded connection. In a development of the first variantembodiment, a reservoir which communicates with the capillary gap,adjoins the liquid container and is separated therefrom by the openableclosure is provided. The reservoir serves, when the closure is open, toreceive at least some of the liquid material from the liquid containerand to ensure the coupling in terms of capillary action to the capillarygap. The openable closure is preferably opened by a pin which is mountedin an axially displaceable manner in the housing and the first end ofwhich is directed toward the openable closure and the second end ofwhich protrudes out of the outer surface of the housing in the manner ofan extension when the closure is closed, by a compressive force beingexerted on the second end. The compressive force is transmitted by thepin to the openable closure, as a result of which the latter is finallytorn open along a predetermined breaking point. The compressive forcecan be produced, for example, by finger pressure. A particularlyadvantageous refinement of the invention relates to an inhalator,comprising an inhalator component as just described, and a reusableinhalator part which is couplable to the inhalator component; accordingto the invention, the second end of the pin is in ram-like operativeconnection to the reusable inhalator part during the coupling, as aresult of which the previously described compressive force is produced.Therefore, the inhalator component is coupled to the reusable inhalatorpart and the liquid container is opened simultaneously by a singlemanipulation.

According to the invention, the reservoir communicates with the chambervia a ventilation duct, as a result of which air passes into thereservoir and compensates for the pressure. By this means, each portionof liquid material which passes into the capillary gap is immediatelyreplaced by a portion of air identical in volume. It is essential thatthe ventilation duct is connected to the chamber and does notcommunicate with the external surroundings since otherwise the suctionpressure would combine with the capillary flow during inhalation, andliquid material would be sucked out of the liquid container inaccordance with the straw principle.

In a second variant embodiment, the liquid container is arranged in thehousing so as to be manually displaceable along a displacement axisbetween two stop positions, and, in the first stop position, the liquidcontainer interacts with a blocking device which is not unlockable, and,in the second stop position, the liquid container interacts with anopening means which opens the openable closure. The blocking devicebasically prevents the liquid container from being removed from thehousing. Therefore, as in the first variant embodiment, the liquidcontainer cannot be removed from the housing—involving the sameadvantages in terms of safety as already described earlier. In adevelopment of the second variant embodiment, the opening meanscomprises a first spike which is formed by the capillary gap andpenetrates the openable closure in the second stop position, thusproducing the coupling in terms of capillary action to the liquidmaterial. Furthermore, a ventilation duct is again provided, the firstend of which communicates with the chamber, and the second end of whichis designed as a second spike which penetrates the openable closure inthe second stop position. The first spike and the second spike thereforetogether form the opening means. The effect of this arrangement issimilar to that of a coupling between a fountain pen and the inkcartridge thereof. Of course, the first spike and the second spike mayalso be combined to form a single common spike. The blocking devicewhich is not unlockable can consist in a simple manner of a projectionwhich is formed, for example, by the housing or the mouthpiece andagainst which the liquid container strikes in the first stop position.Finally, the second variant embodiment is concerned with an inhalatorcomponent, comprising a mouthpiece with a mouthpiece channel throughwhich a user obtains the vapor-air mixture or/and condensation aerosoloffered, and, according to the invention, the displacement axis isorientated at least approximately parallel to the center axis of themouthpiece channel, and, at least in the first stop position, an endsection of the liquid container laterally next to the mouthpieceprojects out of the housing. The displaceable liquid container can bedisplaced in a simple manner into the second stop position thereof bythe user pressing on the protruding end of the liquid container. Themouthpiece and the liquid container protrude out of the housing on thesame end side of the inhalator component, this making the inhalatorcomponent handy and the use of same ergonomic.

Furthermore, according to the invention, a buffer store whichcommunicates with the capillary gap and itself consists of capillariescan be provided. The buffer store has the capability of receiving liquidmaterial from the capillary gap and, when the need arises, of dispensingthe stored liquid material again via the capillary gap to the wickirrespective of position. As a result, the inhalator component can beoperated in any position, at least as long as liquid material is storedin the buffer store. The capillaries can consist, for example, of slots,holes or of a porous material, wherein care should be taken to ensurethat the capillary action or capillary pressure thereof (capillary rise)is lower than the capillary action of the wick, since otherwisecapillary flow does not come about.

As an alternative to the previously described liquid container, theinhalator component can contain a liquid store which is composed of anelastic, open-pored material and is impregnated with the liquidmaterial; according to the invention, the composite is clamped in themanner of a sandwich between one of the two plate-like contacts—asalready described previously—and the liquid store, as a result of whichthe wick is coupled in terms of capillary action to the liquid materialin the liquid store. The elastic, open-pored material can be composed,for example, of a fiber material or of foam. The liquid material isautomatically sucked out of the liquid store into the wick andinfiltrates the latter. A prerequisite is that the capillary action orthe capillary pressure (capillary rise) of the wick is greater than thecapillary action of the liquid store. The sandwich-like clampingconstitutes a structurally simple arrangement which is cost-effective toproduce.

In a development of the invention, the inhalation component contains acondensate binding device for receiving and storing condensate residueswhich are formed in the course of the production of the vapor-airmixture or/and condensation aerosol; considerable quantities ofcondensate residues can occur especially if the liquid material to beevaporated contains relatively large portions of low-boiling fractionswith high vapor pressure, for example ethanol or/and water. Suchportions of low-boiling fractions are advantageous especially for tworeasons and also necessary in the case of the inhalator componentaccording to the invention: firstly, such portions reduce the viscosityof the liquid material, thus enabling the liquid material to infiltratethe wick more rapidly. This effect has proven particularly advantageousin the composite according to the invention, since the thickness of thecomposite and, due thereto, also the average pore diameter of the wickare extremely small. Secondly, the low-boiling fractions cause drugs andother additives contained in the liquid material to more easilyevaporate, and fewer evaporation residues are formed, and the thermaldecomposition of the liquid material is reduced. In order to make saidpositive effects useful to a satisfactory extent, the mass portion ofthe low-boiling fractions should be significantly above 50%. As aconsequence, considerable quantities of condensate residues whichexpediently have to be bonded are anticipated during operation of theinhalator component according to the invention.

According to the invention, the condensate binding device consists of anopen-pored, absorbent body which is arranged spaced apart from, but inthe direct vicinity of the wick capillary structure which is exposed insaid section. The pores of the open-pored, absorbent body receivecondensate deposits formed from the vapor phase and in this respect actin principle in a manner similar to a sponge. Even a relatively largequantity of condensate can easily be bonded. The open-pored, absorbentbody prevents freely moveable condensate accumulations from forming inthe inhalator component, in particular in the chamber, which condensateaccumulations may have an adverse effect on the functioning in theinhalator component but also constitute a risk to the user and theenvironment if said accumulations contain drug residues or poisons, suchas nicotine. The effect achieved by the special arrangement of theopen-pored, absorbent body in the immediate vicinity of the vaporformation zone—i.e. in a region of high vapor density—is that thecondensate residues are absorbed in a very high concentration andtherefore highly effectively, and said condensate residues cannot offerthe opportunity at all of dispersing into peripheral regions. It isparticularly favorable if the open-pored, absorbent body directly coversthe wick capillary structure which is exposed in said section, since thegreatest vapor density should be anticipated in this zone. In anadvantageous refinement of the invention, the open-pored, absorbent bodycomprises two parts or sections which are arranged spaced apart fromeach other, and the composite is at least partially arranged between thetwo parts or sections. Furthermore, it is considered as being accordingto the invention that the open-pored, absorbent body is arranged in thechamber and fills the predominant part of the chamber. This enables aparticularly large absorption capacity for the liquid condensateresidues to be realized with a compact construction. It is furthermorefavorable if the open-pored, absorbent body consists of a dimensionallystable material which substantially retains the shape thereof even aftercomplete infiltration by the condensate residues. In order to establishwhether a specific material is dimensionally stable, it suffices toimpregnate said material with an ethanol-water solution and to check thedimensional stability after a residence period of three days. Thedimensional stability ensures that the flow conditions in the chamber,in particular around the composite, and therefore the conditions forforming the vapor-air mixture or/and condensation aerosol remainconstant. By way of example, the open-pored, absorbent body can consistof a solid, foam-like material, such as metal foam or ceramic foam, of aporous sintered compact, of a porous filling material without swellingtendency, for example of a drying agent and granular material fill, orof a porous fiber composite, for example formed from natural or chemicalfibers interconnected thermally or with the aid of a binding agent. Inaddition, it is essential for the material to be very substantiallychemically inert to the condensate residues.

According to a preferred embodiment of the invention, the open-pored,absorbent body is substantially surrounded by the housing and isconnected nonseparably to the housing. The effect which is thereforeintended to be achieved is for the open-pored, absorbent body not to beable to come into contact directly with the environment, and for removalof said body from the housing to be possible only by the application offorce and destruction of the inhalator component. Said protectivemeasure has proven advantageous especially if the condensate containsdrug residues or/and poisons, such as nicotine. The inhalator componenttogether with the open-pored, absorbent body forms a disposable articlewhich should be disposed of properly after the designated service lifeis reached.

In an advantageous development of the invention, a two-stage condensatedeposition device is provided, consisting firstly of the open-pored,absorbent body and secondly of a cooler through which the vapor-airmixture formed and/or condensation aerosol can pass. This development ofthe invention is suitable in particular for use in drawing inhalators.The cooler cools the vapor-air mixture or/and condensation aerosolpassing therethrough and in the process removes even more condensatetherefrom. The cooler can be formed, for example, by a pore body throughwhich the flow can pass and which is substantially permeable to theparticles of the condensation aerosol formed. In addition to thecooling, the pore body also brings about intimate mixing of thevapor-air mixture or condensation aerosol passing therethrough, as aresult of which the properties of said mixture or aerosol arehomogenized, for example, concentration peaks are reduced. The pore bodytypically consists of a wide-pored material, for example of an open-cellfoam material, of a coarse-pored, porous filling material or of a fibermaterial in the manner of a nonwoven. Synthetic nonwovens manufacturedfrom polyolefin fibers (PE, PP) or polyester fibers should be mentionedas an example of a fiber material in the manner of a nonwoven. The porebody may also be composed of a regenerator material. The regeneratormaterial, with a large surface or heat exchange surface, is capable ofabsorbing a large amount of heat rapidly without substantial flowlosses. Typical regenerator materials include: metal wool, metal chips,metal mesh, wire knits, metal nonwovens, open-cell metal foams, andfills made from metallic or ceramic granular material. Finally, thecooler may also be of multi-stage construction by various porousmaterials being combined with one another. Of course, the invention isnot restricted to the previously enumerated cooler materials. By meansof the cooling and homogenization, the organoleptic properties of thevapor-air mixture or/and condensation aerosol received by the user canbe significantly improved.

In a particularly preferred refinement of the invention, the cooler isformed by a tobacco filling. In addition to the cooling/condensation andhomogenization, the tobacco filling additionally brings aboutaromatization of the vapor-air mixture or condensation aerosol passingtherethrough and is especially appropriate if the liquid materialcontains nicotine as the drug. Moreover, in laboratory tests withproptypes operating in accordance with the drawing inhalator principleand with nicotine-containing drug preparations as the liquid material,further favorable effects have also been established: for example, theinhalability of the nicotine-containing vapor-air mixture andcondensation aerosol could be improved, which can partially beattributed to a certain extent to the effects described above. However,there is the hypothesis that additional operative mechanisms areinvolved—in particular diffusion and adsorption processes relating tothe free, unprotonized nicotine, which still have to be investigated indetail. The filling density of the tobacco filling is upwardlyrestricted by the fact that the filling firstly has to be as permeableas possible to the aerosol particles passing therethrough and, secondly,the induced flow resistance should not be greater than that ofcigarettes. The tobacco filling can be formed from cut tobacco, finelycut tobacco, stuffing tobacco, from a cigar-like bundle of tobacco orfrom comparable or similar forms of tobacco. In particular, dried andfermented tobacco, reconstituted tobacco, expanded tobacco or mixturesthereof are suitable as the tobacco. The tobacco can additionally besauced, spiced, aromatized or/and perfumed. The use of a tobacco fillingas the cooler can also make the change from tobacco products to theinhalator component according to the invention more attractive or/andfacilitate said change. In a preferred development of the invention, itis provided that the volume of the tobacco filling is greater than 3cm³. In separate laboratory tests, it has been shown that theabovementioned effects of the tobacco filling are beneficial in anextent satisfactory for the user only above the previously specifiedminimum value.

According to a further embodiment of the invention, the inhalatorcomponent comprises a mouthpiece opening which is formed by a mouthpieceand communicates with the chamber and through which a user receives thevapor-air mixture or/and condensation aerosol offered, wherein, in thecourse of the inhalation, a flow in the direction of the mouthpieceopening is formed between the air admission opening and the mouthpieceopening, at least part of which flow passes the composite. According tothe invention, at least one air bypass opening is arranged downstream ofthe composite, through which air is additionally fed into the flow fromthe surroundings, and the effective flow cross section of the air bypassopening is at least 0.5 cm². This arrangement makes the inhalatorcomponent also useable for classic inhalators which basically require aslow a flow resistance as possible. The air additionally flowing throughthe air bypass opening (“bypass air”) does not itself pass the compositeand, as a result, also does not have any direct influence on theformation of the vapor-air mixture or/and condensation aerosol and onthe properties thereof. However, there is an indirect influence in sofar as the bypass air reduces the quantity of air (“primary air”)flowing in through the air inlet opening if a constant quantity ofinhalation air is required. The quantity of primary air can thereby bereduced arbitrarily. A reduction in the quantity of primary air results,inter alia, in an increase in the aerosol particles formed; at the sametime, however, the quantity of condensate residues formed alsoincreases, but this can be counteracted by the arrangement of acondensate binding device—as previously described. According to theinvention, a further reduction in the flow resistance and a furtherreduction in the quantity of primary air are obtained by the air bypassopening consisting of two bypass openings which are arranged in oppositehousing sections.

According to the invention, it is furthermore provided that the twobypass openings are adjoined by two guide vanes which point in thedirection of the mouthpiece opening and strive toward each other, andthe free ends of which form a nozzle-shaped mouth opening through whichthe vapor-air mixture formed or/and condensation aerosol flows out ofthe chamber and is subsequently mixed with the air flowing in from thebypass openings. The two guide vanes have the effect of substantiallycovering the chamber to the outside, thus significantly reducing therisk of, for example rainwater or saliva entering the chamber. Inaddition, the exchange of air between the chamber and the surroundingsis also limited, and therefore the natural vaporization of portions ofthe liquid material in the wick is reduced. Such a vaporization canprove unfavorable, in particular during prolonged periods of theinhalator component not being used, in so far as the composition of theliquid material can change, and, in the case of drugs, the dosingthereof may differ from the target.

It is also considered as being according to the invention that a flowhomogenizer is arranged downstream of the air bypass opening, the flowresistance of which flow homogenizer is lower than 1 mbar at an airthroughput of 250 mL/sec. The flow homogenizer is passed through both bythe vapor-air mixture formed or/and condensation aerosol and by thebypass air flowing in through the air bypass opening, and thoroughlymixes and homogenizes said two flow components. Concentration peaks aredissipated, and the homogenized mixture emerging from the mouthpieceopening is more pleasant for the user to inhale. The flow homogenizercan consist by way of example of a material in the manner of a nonwovenor foam; such a material is suitable for producing flow turbulences andeddies to a sufficient degree without exceeding the cited limit valuefor the flow resistance. Only in this way can the inventive refinementjust described be used for a classic inhalator.

In an optional refinement of the invention, a plurality of compositesarranged next to one another and having differing heat capacity isprovided. In a further optional refinement of the invention, a pluralityof composites arranged next to one another and having differing heatingelement properties is provided. In a further optional refinement of theinvention, a plurality of composites arranged next to one another andhaving electric heating elements which are activatable in different waysis provided. In a further optional refinement of the invention, aplurality of composites arranged next to one another is provided, andthe individual composites are assigned liquid materials of differingcomposition for evaporation by the wick of said composites being fed bysources containing different liquid material. The abovementionedrefinement options which, furthermore, can also be combined with oneanother arbitrarily make it possible to configure the evaporationprocess to be more variable in terms of space and time. This variabilitypermits even the complex ratios in the distillation zone of a cigaretteto be approximately simulated.

In a special refinement of the invention, a plurality of compositesarranged next to one another is provided, the heating elements of whichconsist of electric heating resistors; according to the invention, theheating resistors are connected in series to one another. This specialrefinement has proven particularly advantageous if the heating resistorsconsist of a metallic resistance material, for example stainless steelor heating conductor alloys, since the series connection and theassociated increase in resistance enable the heating stream to belimited to an extent which can still be readily controlled by theelectronic activation and by the energy store. Furthermore, by means ofthe increase in resistance, the power density in the composite can bethrottled if required such that stable evaporation can always beensured.

Expedient and advantageous exemplary embodiments of the invention areillustrated in the drawings and are explained in more detail in thedescription below.

In the drawings:

FIGS. 1A, 1B, 1C show, respectively, back, side, and front views of afirst embodiment of an inhalator according to the invention, in the formof a drawing inhalator;

FIGS. 2A and 2B show, respectively, side and front views of an inhalatoraccording to FIG. 1A with a reusable inhalator part and an exchangeableinhalator component in the decoupled state;

FIGS. 3A, 3B, 3C show, respectively, bottom, front and top views of thereusable inhalator part;

FIGS. 4A, 4B, and 4C show, respectively, bottom, back and top views ofthe reusable inhalator part without the battery cover; FIGS. 5A, 5B, and5C show, respectively, side, back (without the switching circuit cover)and back (without the battery) views of the reusable inhaler part;

FIGS. 6A, 6B, and 6C show, respectively, bottom, front, and top views ofthe exchangeable inhalator component;

FIG. 7A shows the exchangeable inhalator component with the liquidcontainer and mouthpiece illustrated separately;

FIGS. 7B and 7C show, respectively, side and cross-sectional views ofthe liquid container shown in FIG. 7A;

FIG. 8 shows the inhalator according to FIG. 1A without the switchingcircuit cover;

FIG. 9 shows a longitudinal section through the inhalator according toFIG. 8 level with the planar composite, wherein the sectional view onthe other side of the composite has been expediently adapted;

FIG. 10 shows a sectional view of the inhalator along the line A-A inFIG. 9 with the switching circuit cover;

FIG. 11 shows a cross section of the inhalator according to FIG. 1Alevel with the planar composite;

FIG. 12 shows the detail a from FIG. 10 in an enlarged illustration;

FIG. 12a shows the detail b from FIG. 12 in an enlarged illustration;

FIG. 13a and FIG. 13b show alternative variant embodiments relating tothe detail a;

FIG. 14a , FIG. 14b and FIG. 15a , FIG. 15b and FIG. 15c show crosssections of various embodiments of planar composites in an enlargedillustration;

FIG. 16 shows a variant embodiment relating to the detail b from FIG. 12with three linear composites arranged next to one another;

FIG. 16a shows a cross section of an individual linear compositeaccording to FIG. 16 in an enlarged illustration;

FIG. 17 shows the detail c from FIG. 11 in an enlarged illustration;

FIG. 18 shows the detail d from FIG. 9 in an enlarged illustration;

FIG. 19 shows a sectional view of the inhalator along the line B-B inFIG. 9 with the switching circuit cover;

FIG. 20 shows a sectional view of the exchangeable inhalator componentalong the line C-C in FIG. 7A and FIG. 11 with the liquid containerindicated;

FIG. 21 shows a second embodiment of an inhalator according to theinvention, in the form of a classic inhalator, in a view analogously toFIG. 9;

FIG. 22 shows a sectional view of the inhalator according to FIG. 21along the line D-D in FIG. 21 with the switching circuit cover;

FIGS. 23A and 23B show, respectively, front and top views of theexchangeable inhalator component of the inhalator according to FIG. 21;

FIG. 24a and FIG. 24b show an exchangeable inhalator component with analternative liquid container system, wherein the inhalator componentaccording to FIG. 24b is illustrated torn open around the liquidcontainer;

FIG. 25 shows a sectional view of the inhalator along the line E-E inFIG. 24 b;

FIGS. 26A, 26B, and 26C show, respectively, first side, first sidewithout a cover for the cartridge, and cross-sectional views of anexchangeable inhalator component with a further alternative liquid storesystem;

FIG. 27 shows a cross section of the inhalator component according toFIG. 26A level with the planar composite;

FIG. 28 shows a section through the liquid store according to FIG. 26Atransversely with respect to the planar composite;

FIG. 29A shows a side view of an exchangeable inhalator component withtwo planar composites arranged next to each other;

FIG. 29B shows a sectional view of the component shown in FIG. 29A,wherein the section runs level with the planar composites.

FIG. 1 shows a first exemplary embodiment of an inhalator according tothe invention, which inhalator in the specific example is in the form ofa drawing inhalator, and the shape and size of which are configured suchthat the inhalator can be handled simply and comfortably by users. Interms of volume, the inhalator is only approximately half the size of acigarette pack. In principle, the inhalator which is illustrated by wayof example consists of two parts, namely of an inhalator part 1 and ofan inhalator component 2. The inhalator component 2 consists of ahousing 3 and comprises, inter alia, a liquid container 4 and amouthpiece 5 in the manner of a tobacco pipe. The liquid container 4contains a liquid material which evaporates in the inhalator component 2and is converted into an inhalable vapor-air mixture or/and condensationaerosol. The vapor-air mixture or/and condensation aerosol formed isoffered to the user via the mouthpiece 5. In principle, all substancesand preparations which can be evaporated in a substantially residue-freemanner under atmospheric conditions are suitable as the liquid material.This condition is even already met if the particular substance or theparticular preparation is present in diluted form, for example isdissolved in water or/and ethanol, and the solution evaporates in asubstantially residue-free manner. By means of a sufficiently highdegree of dilution in an easily volatile solvent, such as ethanol or/andwater, even substances which are otherwise difficult to evaporate canmeet the abovementioned condition, and thermal decomposition of theliquid material can be avoided or significantly reduced.

The liquid material preferably contains a drug. The aerosol particlesproduced by condensation generally have a mass median aerodynamicdiameter (MMAD) of smaller than 2 μm and, as a result, even reach thealveoli. The inhalator according to the invention is suitable inparticular for administering drugs acting systemically, for exampledrugs which deploy the main effect thereof in the central nervoussystem. An example is nicotine, the boiling point of which is at 246° C.The aerosol particles containing the drug are predominantly deposited inthe alveoli where the drug transfers in a flash into the bloodcirculation. With reference to the example of nicotine, it should benoted that the latter reaches its target organ—namely the centralnervous system—in a focused concentration just approximately 7-10seconds after inhalation. Of course, the inhalator in question couldalso be operated without drugs, for example just with aromasubstances—and even in the form of nonmedical applications.

As is explained in more detail below, the inhalator part 1 contains atleast one energy store and an electric switching circuit, wherein theenergy store is protected by a battery cover 6 and the switching circuitby a switching circuit cover 7.

As FIGS. 2A and 2B show, in the specific exemplary embodiment, theinhalator part 1 and the inhalator component 2 are designed so as to bedetachable from each other. The detachable coupling consists of a snapconnection, formed from two snap-in hooks 8 and two latching lugs 9interacting therewith. This arrangement makes the inhalator part 1reusable, this basically being expedient if it is taken intoconsideration that, firstly, the inhalator part 1 does not come intocontact with the liquid material, i.e. is not contaminated by the liquidmaterial, and, secondly, contains components which have a longer lifethan the parts of the inhalator component 2. After the liquid materialin the liquid container 4 has been used up, the inhalator component 2 isas a whole disposed of properly by the user and replaced by a newinhalator component 2. The inhalator component 2 in this respectconstitutes an exchangeable disposable article. Proper disposal isappropriate especially if the liquid material contains drugs becausecondensate residues always form and are deposited in the interior of thehousing 3 of the inhalator component 2 over the course of the formationof the vapor-air mixture or/and condensation aerosol. Residues of theliquid material always also remain in the liquid container 4. Inprinciple, of course, it would also be conceivable to design theinhalator part 1 and the inhalator component 2 as a single part, i.e. soas not to be separable from each other. However, this embodiment appearsto be more uneconomical because, in this case, all of the parts andcomponents of the inhalator, i.e. the inhalator as a whole, form adisposable article for single use. Of course, the present invention alsoincludes this embodiment, wherein, in this case, the entire inhalatorcan be interpreted as the inhalator component.

FIGS. 3 to 5 shows various views of the reusable inhalator part 1 withand without a cover.

The reusable inhalator 1 is essentially composed of the following threehousing parts: the battery cover 6, the switching circuit cover 7 and asupport housing 10 arranged in between. For weight reasons, the threehousing parts are preferably manufactured from plastic. The supporthousing 10 conceals the electric switching circuit 11 and the energystore 12 and comprises a partition 13 which separates the switchingcircuit 11 and the energy store 12 from each other. In the exemplaryembodiment, the electric switching circuit 11 is designed as a printedcircuit board which is populated on one side and is fastened to thepartition 13, for example by an adhesive bonding connection. The energystore 12 preferably consists of a rechargeable battery, for example alithium-ion battery or a lithium-polymer battery, preferably of flatconstruction. At present, these types of battery provide the highestenergy densities and currents and have been used in diverse forms for arelatively long time, wherein the wide use in cell phones should bementioned first. Current is supplied from the battery 12 to the printedcircuit board 11 via two flat contacts 14 which are soldered onto therear side of the printed circuit board 11—also see FIG. 10. The flatcontacts 14 protrude through two somewhat larger windows in thepartition 13. The battery 12 comprises two corresponding contacts (notillustrated) which are pressed against the flat contacts 14, thusproducing a detachable electric contact. The compressive force requiredfor this purpose is preferably produced by a leaf spring (notillustrated) arranged between the battery 12 and the battery cover 6.The battery cover 6 is connected detachably to the support housing 10—bymeans of a screw connection in the exemplary embodiment (see FIG. 1A).Of course, as an alternative, the battery cover 6 could also be designedas a latchable sliding cover. The switching circuit cover 7 isconnected, preferably nonseparably, to the support housing 10, forexample by means of an adhesive bonding or welding connection. This isintended to counter unauthorized manipulation of the switching circuit11. In the normally rare event of a switching circuit defect, the entireinhalator part 1 with the exception of the battery 12 should bereplaced. Further components and properties of the reusable inhalatorpart 1 are described in more detail below.

FIGS. 6 and 7 show various views of the exchangeable inhalator component2. As has already been mentioned, the exchangeable inhalator component 2is essentially formed by the housing 3, and contains, inter alia, theliquid container 4 and the mouthpiece 5 in the manner of a tobacco pipe.The liquid container 4 and the mouthpiece 5 are connected nonseparablyto the housing 3. It is favorable in terms of production to manufacturethe liquid container 4 and the mouthpiece 5 as separate parts and onlyto connect said parts subsequently to the housing 3, for example by anadhesive bonding or welding connection—see FIG. 7A. In principle, ofcourse, it is also conceivable to form the liquid container 4 or/and themouthpiece 5 integrally with the housing 3. For weight reasons, thehousing 3, the liquid container 4 and the mouthpiece 5 are preferablymanufactured from plastic, wherein the properties of the liquid material16 should be taken into consideration when selecting the material forthe liquid container 4. If the liquid container 16 contains nicotine,for example, use may be made of plastics as per U.S. Pat. No. 5,167,242(James E. Turner et al.) and U.S. Pat. No. 6,790,496 (Gustaf Levander etal.).

The liquid container 4 is filled with the liquid material 16 via afilling hole 17, preferably under an inert gas atmosphere, such as argonor nitrogen. A flap-like, openable closure 18 is located on an end sideof the liquid container 4 and is opened by the user, by being pressedin, before the inhalator component 2 is used. The openable closure 18 isdescribed in more detail below. The liquid container 4 is nevercompletely filled with the liquid material 16. Complete filling wouldlead, because of the incompressibility of the liquid material 16, to theflap-like, openable closure 18, which always has a certain degree ofelasticity, no longer being pressed in and being left open. Afterfilling has taken place, the filling hole 17 is sealed in an airtightmanner by a closure cover 19. The closure cover 19 can be, for example,adhesively bonded on or welded on, wherein a heating effect on theliquid material 16 should be avoided as far as possible. As analternative, the filling hole 17 can be designed as a capillary bore,and the filling with the liquid material 16 can take place via aninjection needle. In this case, the closure cover 19 could be omitted,and the capillary bore itself melted shut. Further components andproperties of the exchangeable inhalator component 2 are described inmore detail below.

FIG. 8 shows the inhalator according to FIG. 1A with the switchingcircuit cover 7 lifted off. FIG. 8 shows, inter alia, the snapconnection, consisting of the two snap-in hooks 8 and the correspondinglatching lugs 9, in the coupled, latched-in state. In this case, thesnap-in hooks 8 are designed as extensions of the housing 3 while thelatching lugs 9 are formed by contact elements 20. The contact elements20 are fastened to the support housing 10 of the reusable inhalator part1 by means of an adhesive bonding connection and carry out yet furtherfunctions which will be described in more detail below.

FIGS. 9 to 13 provide more detailed information concerning the inside ofthe inhalator and the basic operation thereof. According thereto, thehousing 3 of the exchangeable inhalator component 2 forms a chamber 21in the interior. As FIG. 11 shows best, the chamber 21 is passed throughby a planar composite 22 according to the invention in the manner of abridge and therefore in a contact-free manner. The planar composite 22has a flat shape in the form of a film or strip and consists of aheating element and a wick. The capillary structure of the wick issuitable for absorbing liquid material 16. The heating element and thewick can be formed in extremely diverse ways and can be connected toeach other. Exemplary embodiments are described in more detail below.The planar composite 22 is mounted with two end sections on twoelectrically conductive, plate-like contacts 23, on the surface of whichsaid composite also has an electric contact connection at the same time.The contact connection takes place preferably either by a planaradhesive bonding connection by means of a conductive adhesive—forexample adhesives from Epoxy Technology, www.epotek.com—or by a weldedconnection. In the case of a welded connection, care should be taken toensure that the wick or the capillary structure thereof is as far aspossible not impaired by the welding. If required, the welding should becarried out merely in a spotwise manner. Information has already beenprovided earlier as regards the selection of material for the plate-likecontacts 23.

In the exemplary embodiment, the region between the two plate-likecontacts 23 defines that heated section of the planar composite 22 whichis arranged in the chamber 21 in a contact-free manner. The arrangementin a contact-free manner results in the heat conduction losses beingequal to zero in the thickness direction of the planar composite 22. Asa result, said section can heat up to an extent such that the liquidmaterial 16 stored in the wick reaches boiling point and evaporates.According to the invention, the capillary structure of the wick in saidsection is substantially exposed at least on one side of the planarcomposite. As is made clear below over the course of the description ofexemplary embodiments of the composite, this side is preferably thatside 24 of the planar composite 22 which faces away from the plate-likecontacts 23. The vapor formed over the course of the evaporation of theliquid material can therefore flow out of the exposed capillarystructure of the wick over a large area and without substantialobstruction. In a second refinement of the planar composite, which islikewise described below with reference to examples, the capillarystructure of the wick in said section is additionally substantiallyexposed on that side 25 of the planar composite 22 which is opposite theside 24, and therefore the evaporation surface and consequently also themaximum evaporative capacity which can be obtained doubles in comparisonto the case first mentioned. The maximum evaporative capacity which canbe obtained is defined by the first occurrence of a boiling crisis inthe wick.

The housing 3 furthermore forms an air admission opening for the supplyof air from the surroundings into the chamber 21. The supplied air mixesin the chamber 21 with the vapor flowing out of the exposed capillarystructure of the wick, over the course of which the vapor-air mixtureor/and condensation aerosol is formed. The air admission opening 26 isdesigned as a slot-shaped channel. The slot-shaped channel is orientedparallel to the planar composite 22. In the exemplary embodimentaccording to FIG. 10 and FIG. 12, the slot-shaped channel is laterallyoffset somewhat with respect to the planar composite 22, namely isarranged on that side of the planar composite on which the capillarystructure of the wick is substantially exposed. The effect achieved bythis arrangement is that the air flowing into the chamber 21 through theslot-shaped channel 26 completely overflows the exposed capillarystructure of the wick, and homogeneous mixing conditions can arise. If aconstant drawing profile (drawing volume, drawing duration) ispresupposed, it is possible, by varying the slot height of theslot-shaped channel 26, to change the flow velocity of the inflowingair, and thereby to influence, within certain limits, the aerosolformation dynamics and, in association therewith, the properties of theaerosol produced. A reduction in the flow velocity allows the aerosolparticles to increase on average in size. The geometrical position ofthe slot-shaped channel with respect to the planar composite 22 also hasan influence on the aerosol formation.

FIGS. 13a and 13b show alternative arrangements of the air admissionopening 26: according thereto, the air admission opening 26 in theexample according to FIG. 13a is formed by two slot-shaped channels 26which are arranged on opposite sides of the planar composite 22. Airflowing into the chamber 21 therefore flows around the planar composite22 on both sides. In the example according to FIG. 13b , the slot-shapedchannel 26 is arranged centrally with respect to the planar composite;in this case, the planar composite 22 lies in the plane of theslot-shaped channel and the inflowing air flows directly onto saidcomposite, wherein the stream of air from the planar composite isdivided into two parts, and consequently, as in the previous example,the flow passes around the composite on both sides. The arrangementsaccording to FIGS. 13a and 13b are suitable especially with that variantembodiment of the planar composite 22 in which the capillary structureof the wick is exposed on both sides, since, in this case, vapor flowsoff from both sides 24 and 25 of the planar composite 22. However, saidarrangements are also suitable for the variant embodiment of the planarcomposite 22 with the capillary structure exposed only on one side in sofar as the second portion of the stream of air, which flows, as it werepassively, around the composite, weakens the first portion of the streamof air, which brings about the aerosol formation, and therefore theproperties of the aerosol formed can again be influenced.

The air admission opening 26 designed in the form of a slot-shapedchannel draws the air out of a plenum chamber 27 which serves todistribute the air uniformly to the slot-shaped channel 26 such thatidentical flow conditions prevail essentially on all sides in theslot-shaped channel. There is a flow throttle 28 upstream of the plenumchamber 27. The flow throttle 28 has the purpose of producing a flowresistance which is similar to that of a cigarette such that, duringdrawing, the user feels a similar drawing resistance as when drawing ona cigarette. Specifically, the flow resistance should be within therange of 12-16 mbar at a volumetric flow rate of 1.05 L/min and shouldhave as linear a characteristic as possible. The flow throttle 28 can beformed, for example, from an open-pored sintered compact made of metalor plastic, with the air passing through the pores therein. For example,porous shaped plastic bodies from Porex, www.porex.com, have provensuccessful in prototypes. In the exemplary embodiment, the plenumchamber 27 is part of the exchangeable inhalator component 2 and theflow throttle 28 is part of the reusable inhalator part 1. In principle,it would also be possible to arrange the plenum chamber 27 and the flowthrottle 28 in the exchangeable inhalator component 2, or alternativelyto arrange both in the reusable inhalator part 1.

FIG. 10 shows the further course of the air flow upstream of the flowthrottle 28. The flow is indicated by arrows. According thereto, theflow throttle 28 draws the air out of a transverse channel 29 which, forits part, opens into the space between the printed circuit board 11 andthe switching circuit cover 7. The actual supply of the air from thesurroundings takes place via a feed opening 30 formed by the switchingcircuit cover 7. The feed opening 30 is arranged on that end side of theinhalator which is opposite the mouthpiece 5. This position providesprotection at the earliest opportunity against the entry of rainwater.

FIGS. 14a, 14b and 15a, 15b, 15c show exemplary embodiments of theplanar composite 22 with reference to cross-sectional illustrations,wherein “cross section” is understood as meaning a section normal to thelongitudinal direction of the composite (cf. FIG. 9). Specifically,FIGS. 14a and 14b show embodiments with a capillary structure exposedonly on one side while FIGS. 15a to 15c show embodiments in which thecapillary structure of the wick is exposed on both sides of the planarcomposite. According to the embodiment as per FIG. 14a , the planarcomposite 22 consists of four layers: namely of a metal foil 31 andthree metal wire meshes 32 sintered thereon. The metal consists ofstainless steel (for example AISI 304 or AISI 316) or of a heatingconductor alloy—in particular from the group of NiCr alloys or CrFeAlalloys (“KANTHAL®”). When stainless steel is used, carbon-reducedcharges are preferred (for example AISI 304L or AISI 316L) because saidcharges are less susceptible to intercrystalline corrosion. The metalfoil 31 in the stainless steel embodiment can be obtained, for example,from Record Metall-Folien GmbH, www.recordmetall.de. The wire mesh canbe obtained, for example, by Haver & Boecker, www.haverboecker.com orSporl KG, www.spoerl.de. The four layers are connected to one another bysintering. The sintering is preferably carried out in vacuo or underinert hydrogen gas. Sinterings of this type belong to the prior art andare routinely carried out, for example, by GKN Sinter Metals FiltersGmbH, www.gkn-filters.com and by Sporl KG, www.spoerl.de. The sinteringadvantageously takes place in the form of a multiple panel; that is tosay, relatively large planar panels, for example in the format200.times.200 mm, are sintered rather than individual planar composites.The individual composites are obtained from the multiple panel aftersintering by means of laser cutting or punching and are subsequentlyoptionally etched in an etching bath.

Table 1 shows by way of example the specifications of planar composites22 used in prototypes.

TABLE 1 Metal foil thickness 10 μm Metal foil material: AISI 304 1stwire mesh layer: 36 × 90 μm Wire diameter × mesh width 2nd wire meshlayer: 30 × 71 μm Wire diameter × mesh width 3rd wire mesh layer: 20 ×53 μm Wire diameter × mesh width Wire mesh material: AISI 316L Compositespan: 14 mm Composite width: 2-5 mm Composite thickness: 140-160 μmEtching rate: up to 50% Avesta pickling bath 302*) Porosity: 65-80%Depending on the etching rate *)Manufacturer: Avesta FinishingChemicals, www.avestafinishing.com

The composite span corresponds to that section in the chamber 21 whichthe composite 22 spans in a contact-free manner; in the specificexemplary embodiment, this section corresponds to the distance betweenthe two plate-like contacts 23. The composite span and the compositewidth have an opposed influence on the resulting heating elementresistance. The etching rate defines the mass loss obtained as a wholeby the etching. The first wire mesh layer rests directly on the metalfoil 31. The third wire mesh layer forms the top layer and at the sametime the exposed capillary structure of the planar composite 22. Theplanar composite 22 is preferably mounted by the metal foil 31 on theplate-like contacts 23. The electric contact connection of the metalfoil 31 preferably takes place via a planar adhesive bonding connectionbetween the metal foil 31 and the electrically conductive plate-likecontacts 23. In principle, the contact connection could also be producedby a welded connection. A planar composite 22 having a contactconnection in such a manner and the specifications as per table 1, witha composite width of 2 mm and an etching rate of 35% has a heatingelement resistance of approximately 310 mOhm. When heating conductoralloys are used instead of stainless steel, the heating elementresistance can be significantly increased; specifically, when DINmaterial number 2,4872 (NiCr20AlSi) is used, by a factor of 1.8 incomparison to AISI 304/AISI 316, and, when DIN material number 1,4765(CrA1255) is used, even by a factor of 2.0. In consequence, a planarcomposite with a composite width of 5 mm in an embodiment with DINmaterial number 2,4872, but with otherwise identical specifications,would have, as indicated previously, a heating element resistance ofapproximately 225 mOhm. If energy is supplied on the basis of alithium-polymer cell with a nominal or idling voltage of 3.7 V and auseful voltage under load of approx. 3.1 V, the current flowing throughthe planar composite is calculated, on the basis of Ohm's law, at 10 A(for 310 mOhm) or 13.8 A (for 225 mOhm). Said current strength caneasily be obtained from current lithium-polymer cells. In a furtherstep, the electric nominal power is calculated, this being at the sametime the maximum heating power which can be realized, at 31 W (for 310mOhm) or 42.7 W (for 225 mOhm). As is also described below, said powerscan be reduced arbitrarily by the electric switching circuit 11.

On the basis of the previously cited specifications of an exemplaryplanar composite with a composite width of 5 mm and an etching rate of35%, the pore volume of the planar composite 22 in the section of thecomposite span (evaporation section) is calculated at approximately 7.5μL. This volume is filled by the liquid material 16 to be evaporated andcorresponds to the maximum amount of liquid material which can beevaporated per drawing or inhalation (intermittent inhalator operation).If the liquid material contains, for example, nicotine as the drug in aconcentration of typically 1.5% by volume, then this theoreticallyresults in a maximum nicotine dose released of 110 μg per evaporation ordrawing or, calculated on the basis of 10 inhalations, an overall doseof 1.1 mg. For various reasons, the maximum obtainable dose can actuallybe somewhat below the calculated values. It is essential, however, thatthe nicotine doses of current cigarettes (0.1-1.0 mg) can easily beadministered by the inhalator according to the invention. It isfurthermore essential that the active compound dose can be reducedarbitrarily, either by a reduction in the active compound concentrationin the liquid material, or by the selection of a smaller compositewidth, or by throttling of the heating power supplied by means of theelectric switching circuit 11. The latter measure also counteractsthermal decomposition of the liquid material 16, since the composite 22is not heated up as highly.

It should be noted that both the metal foil 31 and the metal wire mesh32 sintered onto the foil make a contribution to the electric heatingresistor. The electric heating resistor can be interpreted in thisrespect as a parallel connection of said individual resistors. Thecapillary action of the wick in interaction with the wire mesh 32 isalso established by the metal foil 31, wherein even an individual wiremesh layer in combination with the metal foil 31 can produce a capillaryeffect. Of course, the invention is not restricted to the previouslymentioned specifications. It would also be possible, instead of themetal wire mesh 32, to arrange other open-pored structures made of metalon the metal foil 31; furthermore, a fabric or other open-poredstructures made of electrically nonconductive material, for examplequartz glass, could also be arranged on the metal foil 31 or frittedthereon.

FIG. 14b shows a second exemplary embodiment of a planar composite 22with a capillary structure exposed only on one side. This embodimentdiffers from that according to FIG. 14a only in that, instead of theouter two wire mesh layers, a fiber composite is provided in the form ofa nonwoven fabric which is sintered onto the first wire mesh layer 32.Nonwoven fabrics 33 of this type in the stainless steel embodiment canbe manufactured according to customer specification, for example by GKNSinter Metals Filters GmbH, www.gkn-filters.com. The nonwoven fabric 33preferably has a thickness of 100-300 μm and a porosity >70%. Incomparison to the wire meshes 32, the nonwoven fabric 33 forming theexposed capillary structure of the wick has a significantly largersurface; the larger surface has a favorable effect on the evaporationprocess. Of course, the nonwoven fabric 33 may also be produced from aheating conductor alloy—in particular from the group of NiCr alloys orCrFeAl alloys (“KANTHAL®”); for this purpose, only the raw fibersforming the nonwoven fabric 33 have to be produced in said materialspecifications. The planar composite 22 can optionally be re-etchedafter sintering.

FIG. 15a shows an embodiment of a planar composite 22 with a capillarystructure exposed on both sides. The planar composite accordinglyconsists of an open-pored sintered structure formed from a homogeneous,granular, fibrous or flocculent sintered composite 34. The production ofthin porous sintered composites has long been known. U.S. Pat. No.3,433,632 (Raymond J. Elbert) describes, for example, a method forproducing thin porous metal plates with a thickness of from 75 μm and apore diameter of between 1-50 μm. Among other things, powders wereprocessed from nickel and stainless steel (AISI 304). Porosities of upto 60% and, in one variant embodiment with a multi-layered construction,porosities even up to 90% (but only in the top layers) are achieved.U.S. Pat. No. 6,652,804 (Peter Neumann et al.) describes a similarmethod. JP 2004/332069 (Tsujimoto Tetsushi et al., Mitsubishi MaterialsCorporation) describes a developed process for producing thin poroussintered composites made of metal in the preferred thickness range offrom 50-300 μm, the process being distinguished in that removablefillers, in the specific case acrylic resin spherules, are admixed tothe metal powder to be processed. The acrylic resin spherules arespacers which, over the course of a heat treatment, and even before theactual sintering, sublimate at approximately 500° C. in vacuum virtuallywithout any residue and leave behind cavities, which cavities alsoremain during and after the sintering. By this means, flat compositesconsisting of stainless steel of the specification AISI 316 L wereproduced with porosities of typically 70-90%. The Institute for EnergyResearch (IEF) of the Julich Research Center,www.fz-juelich.de/ief/ief-1 is likewise capable of producing thin porousmetal foils of up to a thickness of 500 μm. Like the abovementionedprocess, the production method is based on the “doctor-blade filmcasting process”.

In principle, all of the abovementioned processes can be used forproducing a planar sintered composite 22, 34 according to the invention,with the process according to JP 2004/332069 being preferred because ofthe high degree of porosity obtained. Care merely has to be taken toensure that the average pore diameter in the homogeneous sinteredcomposite is as far as possible >10 μm in order to ensure sufficientlyrapid infiltration of the wick with the liquid material 16. The grainsize of the metal powder to be processed and of the acrylic resinspherules should be tailored to said condition. The preferred thicknessrange of 50-300 μm, which is cited in the process according to JP2004/332069, is covered by the thickness range particularly preferredfor the planar composite 22.

In addition to processing stainless steel, the abovementioned processesare also suitable for processing pulverulent heating conductor alloysand pulverulent ceramic resistance materials.

FIG. 15b shows a development or modification of a planar composite asper the embodiment according to FIG. 15a by channels or arteries 35which are oriented in the longitudinal direction of the composite andthe advantageous effects of which have already been described earlierbeing arranged in the planar composite 22. The production of saidchannels 35 requires adaptation of the abovementioned productionprocesses by removable threads, for example sublimable acrylic resinthreads, being inserted into the film casting slip by oxidation,sublimation or chemical decomposition. The threads are spacers which,upon being removed, leave behind cavities forming channels 35. This isbest carried out in three process steps: first of all a first film layeris cast. A layer of threads which are oriented parallel to one anotherand later form the arteries 35 is placed into said film layer. Finally,a second film layer which at the same time forms the top layer is cast.For better handling, the threads, prior to the application thereof, areclamped into an auxiliary frame. In this modified embodiment, the grainsize of the metal powder to be processed and optionally of the acrylicresin spherules is preferably within the range of 1-10 μm while thepreferred diameter range of the threads is 20-150 μm. In an optionalprocess step following the film casting and sintering, the planarsintered composite 22, 34 is perforated in the thickness direction, as aresult of which holes 36 are formed. The perforation can be carried out,for example, by means of a laser. The grid of holes should be selectedto be as nonuniform as possible; this is because, with a uniform grid,the unfavorable situation could occur in which all of the holes 36 cometo lie between the arteries 35, and the arteries are not cut. In thiscase, only some of the advantageous perforation effects, which havealready been described earlier, would occur.

To further increase the porosity and the electric resistance, thecomposites as per the embodiments according to FIGS. 15a and 15b canoptionally be re-etched after the sintering. The fastening and contactconnection of the planar sintered composite 22, 34 on the plate-likecontacts 23 are preferably carried out by means of a welded connection.An adhesive bonding connection is possible only if the adhesive used hasa sufficiently pasty or viscous consistency. Otherwise, there would bethe risk of the adhesive entering the pore structure of the compositeand having an adverse effect on the capillary action of the wick. It maypossibly be advantageous to expose the perforation of the composite inthe region of the adhesive bonding connection.

FIG. 15c finally shows a further embodiment of a planar composite 22with a capillary structure which is exposed on both sides. Accordingthereto, the planar composite 22 consists of an open-pored foam 37formed from an electric resistance material. The production of foam-likecomposites has long been known. For example, U.S. Pat. No. 3,111,396(Burton B. Ball) already describes a process for producing metal foams,ceramic foams and graphite foams. The process involves an organic,porous structure being impregnated with a slip containing thefoam-forming material, and the organic structure is decomposed over thecourse of a subsequent heat treatment.

In this manner, inter alia, foams consisting of nickel and nickel basealloys have been produced. For a planar composite 22 according to theinvention, thin, film-like foams having a thickness within the range of100-500 μm, a preferred pore diameter within the range of 20-150 μm anda porosity of >70% are required. A foam material of this type in astainless steel embodiment (for example AISI 316L) can be obtained fromMitsubishi Materials Corporation, www.mmc.co.jp.

The starting point in this case is a standard foam material with athickness of 0.5 mm, a pore diameter within the range of 50-150 μm and aporosity of circa 90%, which material can be compressed arbitrarily inthickness to approximately 100 μm by rolling. The compressed materialcan subsequently optionally also be sintered. Of course, the compressionalso results in a reduction in the porosity, but the porosity can beincreased again, if required, during a final etching treatment.

Although the method for producing the standard foam material is based onprocessing a slip, it differs from the previously described processaccording to U.S. Pat. No. 3,111,396 in that the foam is actually formedby a foaming or blowing agent added to the slip. Of course, heatingconductor alloys—in particular from the group of NiCr alloys and CrFeAlalloys (“KANTHAL®”) can also be processed. The planar composite 22 canconsist of a single foam layer or of a plurality of foam layers sinteredtogether. In order to increase the stability and strength of the planarcomposite 22, the foam 37 can optionally be sintered onto a thin supportlayer 38, for example onto a wire mesh consisting of stainless steel ora heating conductor alloy. With regard to the fastening and contactconnection of the foam 37 on the plate-like contacts 23, the sameapplies as already explained in conjunction with the embodiments as perFIGS. 15a and 15 b.

All of the previously described embodiments of the planar composite 22merely constitute exemplary embodiments. The invention is in no wayrestricted to said exemplary embodiments. For example, a planar foammaterial could be sintered onto a metal foil. Furthermore, anopen-pored, porous deposition layer could be applied to a metal foil—forexample following the process according to DE 1,950,439 (Peter Batzieset al.). Finally, of course, the planar composite could also be formedfrom nonmetallic materials, such as carbon fibers or graphite fibers,for example in the form of woven and nonwoven fabrics, or from quartzglass, for example in the form of a granular or fibrous sinteredcomposite, wherein, in the latter case, a conductive thin layer appliedto the glass surface could bring about the electric resistance heating.Quartz glass is distinguished by high chemical resistance and thermalshock resistance.

FIG. 16 and FIG. 16a show an exemplary embodiment of a linear composite39, wherein, in the present exemplary embodiment, three linearcomposites 39 a, 39 b, 39 c (39 c is not illustrated) arranged parallelto one another are provided. By means of the provision of a plurality oflinear composites, the evaporation surface can be significantlyincreased in comparison to an individual linear composite, if startingfrom the same total cross section. The individual composites do notabsolutely have to have identical properties. For example, it ispossible to assign different heat capacities or/and different heatingelement properties to the individual composites 39 a, 39 b, 39 c. Theresultant effects have already been explained earlier.

In the specific example, the linear composites are designed aswire-shaped sintered composites with an open-pored sintered structure34. The wire-shaped sintered composites 39 a, 39 b, 39 c are mounted inrecesses 108 on the plate-like contacts 23, thus positioning thewire-shaped sintered composites. In the specific exemplary embodiment,the electric contact connection takes place by means of clamping by thewire-shaped sintered composites 39 a, 39 b, 39 c being pressed againstthe plate-like contacts 23 (see arrow in FIG. 16a ) by a ram 40 in themanner of a scaffold. The wire-shaped sintered composites 39 a, 39 b, 39c are preferably produced by means of an extrusion process, for exampleas per AU 6,393,173 (Ralph E. Shackleford et al.). AU 6,393,173describes the production of stainless steel wires having a wire diameterof 0.3-2.0 mm. This diameter range at any rate also covers the preferreddiameter range for the linear composite according to the invention. Theproduction process is based specifically on the extrusion of a mixtureconsisting of a metal powder, a binding agent and a plasticizing agent,and on sintering the extrudate. The metal powder can be in a granular,fibrous or flocculent form. The process has to be adapted in order toobtain an open-pored, porous sintered compact. The adaptation involves aremovable filler, for example sublimable acrylic resin spherules, beingadmixed to said mixture. The acrylic resin spherules are spacers which,over the course of a heat treatment at approximately 500° C. even beforethe actual sintering, subliminate virtually without any residue andleave behind cavities. The binding and plasticizing agents canoptionally be matched to the type and quantity of addition of thefiller. The particle size of the metal powder to be processed and of theacrylic resin spherules should be coordinated in such a manner that theaverage pore diameter of the resulting homogeneous sintered composite isas far as possible >10 μm; this ensures sufficiently rapid infiltrationof the wick with the liquid material 16. Of course, instead of stainlesssteel powder, powders of heating conductor alloys—in particular from thegroup of NiCr alloys and CrFeAl alloys (“KANTHAL®”) can be extruded andsintered in accordance with the process.

It is generally intended for the composites 22 and 39 to be cleanedprior to the installation thereof, and for the surface of the capillarystructure to be activated. This measure brings about improved wetting ofthe composite material by the liquid material 16 and, associatedtherewith, more rapid infiltration of the wick. In the case of stainlesssteel, for example, treatment with 20% strength phosphoric acid sufficesin order to obtain the previously mentioned effects.

The supplying of the composite 22 and 39 with the liquid material 16will be described in more detail below. The following embodiments applyequally to planar and linear composites 22, 39, although the figures arerestricted to illustrating only one embodiment of the composite. As FIG.12a and FIG. 17 and also FIG. 16 and FIG. 16a show, one end of thecomposite 22, 39 projects into a capillary gap 41. The capillary gap 41feeds the wick of the composite with the liquid material 16; as can begathered from the figures, the cross section of the capillary gap 41 islarger than the cross section of the composite 22, 39. This has theeffect that the liquid material 16 primarily flows through the clearcross section of the capillary gap 41 to the evaporation zone, as aresult of which the wick can be infiltrated more rapidly, and thewaiting time between two drawings or inhalations can be shortened. Theeffect acts at least as far as the opening of the capillary gap 41 intothe chamber 21. From this point, only the wick of the composite 22, 39is responsible for transporting the liquid. The capillary gap 41 isbasically formed by one of the two plate-like contacts 23 and an upperpart 42, which is placed in a planar manner onto said capillary gap, bycorresponding recesses forming the capillary gap 41 being incorporatedinto the upper part 42 and into the plate-like contact 23 —see FIG. 12aand FIG. 17. It should be noted that even an individual recess, whetherarranged in the upper part 42 or in the plate-like contact 23, wouldsuffice to form a capillary gap 41. When a planar composite 22 is used,it is at any rate advantageous to arrange the recess in the plate-likecontact 23 since, in this case, the recess can be used at the same timeas a positioning aid for the composite 22. The upper part 42 is joinedto the plate-like contact 23 preferably by means of an adhesive bondingconnection and is composed of a material which is readily wettable withthe liquid material 16, preferably of light metal or of a wettableplastic; the wettability and, moreover, also the adhesive bondability ofplastics can be considerably improved by surface activation, for exampleby a plasma treatment using oxygen as the process gas.

Further upstream, the capillary gap 41 is formed by two thin plates 43which are arranged parallel to and at a distance from each other (seeFIG. 17), wherein one plate is connected to the upper part 42 and theother plate to the plate-like contact 23, preferably by means of anadhesive bonding connection. The plates 43 can be punched, for example,from a stainless steel strip. As FIGS. 18-20 best show, the plates 43forming the capillary gap 41 project into a reservoir 45 via anextension 44. The reservoir 45 directly adjoins the liquid container 4and is separated therefrom only by the flap-like, openable closure 18.The openable closure 18 is opened with the aid of a pin 46. The pin 46is mounted in an axially displaceable manner in the housing 3 andpreferably consists of stainless steel. A first end 47 of the pin 46 isdirected toward the openable closure 18. When the closure 18 is stillclosed, a second end 48 projects in the manner of an extension out ofthe outer surface of the housing 3. The second end 48 of the pin 46 isin ram-like operative connection to one of the two contact elements 20of the inhalator part 1 by the contact element 20, over the course ofthe coupling of the inhalator component 2 to the inhalator part 1, beingpressed against the second end 48 of the pin 46, and the pin 46 beingdisplaced as a result into the housing 3. The compressive force exertedby the contact element 20 is transmitted from the pin 46 to the openableclosure 18. The openable closure 18 has, over the circumference thereof,a material weakening 49 which is dimensioned in such a manner that, uponpressurization by the pin 46, said material weakening tears open over awide circumferential region in the manner of a predetermined breakingpoint, but forms a hinge 50 on one side. This has the effect of theopenable closure 18 opening in the manner of a flap. The pin 46 has, inthe vicinity of the first end 47, a cross-sectional widening 51 which,in the manner of a stop, prevents the pin from being able to slide outof or be removed from the housing 3.

The supplying of the composite 22, 39 with the liquid material 16 willbe explained in summary below, wherein FIG. 18 and FIG. 20 illustratethe flow conditions by means of arrows: over the course of the couplingof the inhalator component 2 to the reusable inhalator part 1, theflap-like closure 18 is opened via the pin 46 and, in consequence, thereservoir 45 is flooded by liquid material 16 under the effect ofgravitational force. The liquid levels before and after the flooding areshown in FIG. 19. The capillary gap 41 sucks up the liquid material 16via the extension 44 and supplies said material to the composite 22, 39,as a result of which the wick is finally completely infiltrated with theliquid material 16. The extension 44 which is formed by the plates 43 isintended to avoid gas bubbles which could obstruct the coupling in termsof capillary action from accumulating in the mouth region of thecapillary gap 41. Furthermore, a ventilation duct 52 which connects thereservoir 45 to the chamber 21 is incorporated into the plate-likecontact 23. The function of the ventilation duct 52 has already beenexplained earlier. The ventilation duct opens into the chamber 21,preferably at a location upstream of the composite 22, 39, sincecondensate deposits should scarcely be anticipated in this region of thechamber 21; this is because such condensate deposits could block theventilation duct 52 or pass via the ventilation duct 52 into thereservoir 45 and contaminate the liquid material 16 stored there.Finally, a buffer store 53 is integrated into the upper part 42 —alsosee FIG. 11 and FIG. 17, the effect of which has likewise already beenexplained earlier. In the present exemplary embodiment, the buffer store53 consists of slots 54 which are arranged parallel to one another andare incorporated into the upper part 42. The slots 54 communicate withthe capillary gap 41 via openings 55 and with the chamber 21 via aventilation gap 56. The capillary action of the slots 54 causes theliquid material 16 to flow out of the reservoir 45 via the capillary gap41 and via the openings 55 into the slots 54 where said material istemporarily stored and can be removed again by the wick as the needarises.

FIGS. 9-12 furthermore show a condensate binding device which isarranged in the chamber 21 and consists of two open-pored, absorbentbodies or sponges 57. The effects of the condensate binding device andthe necessity thereof for the inhalator component according to theinvention have already been explained in detail earlier. The two sponges57 are of plate-like design and are arranged at a distance from andparallel to each other, with the composite 22 being covered on bothsides by the two sponges 57. A flow duct 58 is formed between the twosponges 57, and the formation of the vapor-air mixture or/andcondensation aerosol takes place therein. The main portion of thecondensate residues is separated off at the wall sections 59 of thesponges 57, said wall sections forming the flow duct 58, and isimmediately sucked up by the open pore structure of the sponges. Thesponges 57 are fastened to two opposite walls of the chamber 21, forexample by means of an adhesive bonding connection, fill the predominantpart of the chamber 21 and are preferably composed of a highly porousand dimensionally stable material which is as fine-pored as possible.This is because, if coarse-pored material is used, there is the riskthat, in the event of abrupt movements or accelerations of the inhalatorcomponent 2, the capillary forces of the sponge material will no longerbe sufficient to retain the liquid condensate, and some of thecondensate will be hurled out of the sponges 57. Fiber composites formedfrom natural or chemical fibers connected to one another thermally orwith the aid of a binding agent have proven particularly suitable as thesponge material. Filtrona Richmond Inc.,www.filtronaporoustechnologies.com, specializes in the production offiber composites of this type, with the processing including celluloseacetate fibers bonded by means of triacetin and thermally bondedpolyolefin and polyester fibers.

The sponges 57 are arranged somewhat spaced apart from the upper part 42and from the plate-like contact 23 connected to the upper part 42 suchthat a gap 60 is formed. The gap 60 ensures that the ventilation duct 52and the ventilation gap 56 can communicate unhindered with the chamber21. The sponges 57 should be dimensioned in such a manner that the porevolume thereof is capable of absorbing the anticipated quantity ofcondensate residues formed. The quantity of condensate depends primarilyon the portion in the liquid material 16 of low-boiling fractions with ahigh vapor pressure and on the air throughput through the air admissionopening 26 and through the flow duct 58. If less air is put through,less vapor can be absorbed by the air before being saturated.

As FIGS. 9-10 and FIG. 12 show, a cooler 61 is arranged after thesponges 57 downstream of the composite 22, said cooler, in the specificexemplary embodiment, consisting of a porous filling material 61,through the pores of which the vapor-air mixture or/and condensationaerosol formed can pass. The essential effects of the cooler and fillingmaterial 61 have already been explained in detail earlier. The fillingmaterial 61 is located in a filling space 62 which is bounded on theflow inlet side by a perforated wall 63, on the flow outlet side by themouthpiece 5, and on the casing side by the housing 3 and by a wall ofthe liquid container 4. The perforated wall 63 supports the fillingmaterial 61 and at the same time stiffens the housing 3. The perforatedwall 63 is arranged spaced apart somewhat from the sponges 57—see FIG.12. The effect achieved by this is that the vapor-air mixture or/andcondensation aerosol emerging from the flow duct 58 can be distributeduniformly over the entire cross section of the filling material 61 evenbefore the perforated wall 63, and the flow passes uniformly through thefilling material 61. So that the filling material 61 cannot escape fromthe holes of the perforated wall 63, a first wire mesh 64 is arrangedbetween the filling material 61 and the perforated wall 63. On themouthpiece side, the filling material 61 is bounded by a second wiremesh 65 which prevents the filling material from being able to pass intothe mouthpiece channel 66 or even into the user's mouth cavity. Betweenthe second wire mesh 65 and the mouthpiece channel 66, the mouthpieceforms a collecting chamber 67 causing the flow also to pass uniformlythrough the filling material 61 in the end section. The second wire mesh65 is advantageously fastened directly to the mouthpiece 5, for exampleis melted onto the latter. During installation, first of all the firstwire mesh 64 is placed onto the perforated wall 63. A predefinedquantity of filling material 61 is then introduced into the fillingspace 62, with it also being possible for the filling to take place inmultiple stages, and the filling material 61 being compressed in betweenafter each partial filling. This enables a homogeneous filling densityto be obtained. As an alternative, the filling material 61 could alreadybe pre-packed outside the inhalator component 2, for example in papercylinders, with the cross section matched to the filling space 62, andthe pack inserted into the filling space 62. Packs of this type can beobtained economically from an endless strand. Finally, the mouthpiece 5is fitted and the filling space 62 closed.

The filling material can be composed, for example, of a regeneratormaterial. It has proven particularly advantageous, especially if theliquid material 16 contains nicotine, to use tobacco as the fillingmaterial 61. In prototypes, excellent results have been obtained inrespect of the organoleptic effects of the vapor-air mixture orcondensation aerosol administered, on the basis of finely cut tobaccoand a filling volume of approximately 7 cm.sup.3. The tobacco canadditionally be aromatized by aromatic additives and essential oils, forexample tobacco extract, tobacco aroma oils, menthol, coffee extract,tobacco smoke condensate or a volatile aromatic fraction of a tobaccosmoke condensate being added thereto. Of course, the invention is notrestricted to this selection.

The filling density of the filling material 61 determines the flowresistance offered by the filling material 61 to the vapor-air mixtureor condensation aerosol; the filling density should be coordinated withthe flow resistance of the flow throttle 28 in such a manner that theresulting flow resistance lies within the range already mentioned of12-16 mbar at an air throughput of 1.05 L/min. In principle, it is alsopossible to entirely omit the flow throttle 28, and to produce thedesired flow resistance solely by means of the filling material 61 bythe filling density thereof being correspondingly increased. In general,however, it should be taken into consideration that a filter effect isundesirable; the aerosol particles produced in the chamber 21 should beable to pass through the filling material 61 as far as possible withoutloss. The alternative variant embodiment without a flow throttle 28 alsohas effects on the sensor detection of the beginning of the drawing,which effects will be explained in more detail further on. If thefilling material 61 contains tobacco or/and aroma substances, theinhalator component 2 should be stored up to use thereof in an airtightpackaging in order to prevent aroma substances from escaping. Even afterthe inhalator component 2 is coupled to the inhalator part 1, it ispossible, by closing the mouthpiece channel 66, for example by means ofa cap or a stopper (not illustrated), to substantially prevent aromasubstances from escaping and vaporizing and fractions of the liquidmaterial 16 stored in the wick from escaping.

FIGS. 21-22 show a second exemplary embodiment of an inhalator accordingto the invention, and FIGS. 23A and 23B show an exchangeable inhalatorcomponent for said inhalator. In the specific example, the inhalator isdesigned as a classic inhalator and is based substantially on thearrangement according to FIGS. 9-10, but differs therefrom in that asignificantly larger quantity of air can be put through, as a result ofwhich direct inhalation into the lungs is possible in a single step. Theinhalator differs from the arrangement according to FIGS. 9-10specifically in that both the flow throttle 28 and the second open-poredbody are omitted, and the mouthpiece channel 66 has a substantiallylarger cross section. The flow resistance is decisively reduced in thismanner. A further essential difference consists in that the main portionof the air put through does not pass the composite 22, 39 at all butrather only flows into the inhalator downstream of said composite. Forthis purpose, two bypass openings 68, the common cross section of whichis substantially larger than the cross section of the air admissionopening 26, are arranged on opposite sides of the housing 3 downstreamof the composite 22, 39. The two bypass openings 68 are adjoined by twoguide vanes 69 which are formed by the housing 3, point in the directionof the mouthpiece channel 66 and strive towards each other, and the freeends or tips 70 thereof form a nozzle-shaped mouth opening 71 throughwhich the vapor-air mixture or/and condensation aerosol formed flows outof the chamber 21 and is subsequently mixed with the air flowing in fromthe bypass openings 68. The effects of the guide vanes 69 have alreadybeen explained earlier. For better mixing of the vapor-air mixtureor/and condensation aerosol with the bypass air flowing in through thebypass openings 68, a flow homogenizer 72 can optionally be arranged inthe mouthpiece channel 66—see FIG. 22. The flow homogenizer 72 can bemanufactured, for example, from a synthetic fiber material in the mannerof a nonwoven fabric. Freudenberg Vliesstoffe KG,www.freudenberg-filter.com, provides a material of this type in the formof mats/plates under the name VILEDON®-filter mats. The material can bemanufactured in accordance with the customer's specification. Inparticular, the material properties can be coordinated in such a mannerthat the final product is very substantially permeable to the fineparticles of the condensation aerosol produced, and the flow resistancelies within the desired range already specified earlier. The mats/platesare manufactured from polyolefin fibers (PE, PP) or polyester fibers andcan be further processed by punching.

FIGS. 24-25 show an exchangeable inhalator component 2 of an inhalatoraccording to the invention with an alternative liquid container system.Although, in the specific example, the exchangeable inhalator component2 constitutes an inhalator component for use in a classic inhalator, thealternative liquid container system illustrated can also be used in aninhalator component of a drawing inhalator, as previously described. Asthe figures show, the liquid container 4 is arranged in the housing 3 soas to be displaceable manually along a displacement axis Y between twostop positions. FIG. 24b shows the liquid container 4 in the first stopposition which at the same time defines the starting position of saidliquid container. The first stop position is defined by a projection 73,which is formed by the mouthpiece 5, in interaction with a catch 74formed by the liquid container 4. The projection 73 makes it impossibleto remove the liquid container 4, which optionally contains drugs or/andpoisons, from the inhalator component 2. The catch 74 at the same timesecures the liquid container against rotation by the catch 74 engagingin a corresponding groove 75 in the housing 3. In the starting position,an end section of the liquid container 4 projects out of the housing 3laterally next to the mouthpiece 5. The displaceable liquid container 4can be displaced in a simple manner into the second stop positionthereof by the user pressing the projecting end of the liquid container4. In the process, the liquid container 4 is displaced by the distances. The second stop is formed by the upper part 42 and the plate-likecontact 23 which is connected thereto. The venting opening 76 and theventing duct 77 prevent interfering air cushions from forming during thedisplacement operation. On the end side facing the second stop, theliquid container 4 has two openings 78, 79 which are closed on theinside of the container by means of a film seal 80. The capillary gap 41is substantially identical to the arrangement already described earlier.The plates 43 again form an extension in the form of a first spike 81.The first spike 81 is positioned in such a manner that it is alignedwith the first opening 78 and penetrates the latter in the second stopposition. The obliquely pointed end of the first spike 81 at the sametime cuts through the film seal 80 and enters into contact with theliquid material 16, as a result of which finally the coupling in termsof capillary action to the capillary gap 41 is produced. The spikebehaves in the same manner with the ventilation duct 52: in contrast tothe arrangement described earlier, in the specific exemplary embodimentsaid ventilation duct is integrated into the upper part 42 and, like thecapillary gap 41, forms an extension or second spike 82 at the endfacing the liquid container 4, said extension or spike being positionedso as to be aligned with the second opening 79 in the liquid container 4and to pass through said opening in the second stop position. The secondend of the ventilation duct communicates in turn with the chamber 21(not illustrated). The supplying of the composite 22, 39 with the liquidmaterial 16 functions in precisely the same manner as already describedearlier. In the delivery state of the inhalator component 2, the liquidcontainer 4 is in the starting position thereof, i.e. in the first stopposition. The liquid container 4 is preferably displaced into the secondstop position and coupled to the capillary gap 41 only shortly beforeuse of the inhalator component 2. In order to prevent a premature,unintentional coupling, the liquid container 4 is fixed in the startingposition thereof. The fixing can take place, as FIG. 24b shows, forexample by means of a small semicircular locking plate 109 which isconnected via microwebs 83 to the liquid container 4 and to the housing3. The small locking plate 109 thereby produces a rigid connectionbetween the liquid container 4 and the housing 3. By means of manualapplication of force to the small locking plate 109—for example byrepeated bending thereof—the microwebs 83 can be broken and the fixingof the liquid container 4 undone. As an alternative, the liquidcontainer 4 can be fixed in a simple manner by means of an adhesive tape(not illustrated). Information has already been provided earlier withregard to the selection of material for the liquid container 4, saidinformation applying equally to the specific exemplary embodiment.

FIGS. 26-27 show an exchangeable inhalator component 2 of an inhalatoraccording to the invention with a further alternative liquid storagesystem. Although, in the specific example, the exchangeable inhalatorcomponent 2 constitutes an inhalator component for use in a classicinhalator, the alternative liquid storage system illustrated can also beused in an inhalator component of a drawing inhalator, as describedearlier. In the specific exemplary embodiment, the liquid store containsan open-pored foam 84 which is impregnated with the liquid material 16.The composite 22, 39 is clamped in the manner of a sandwich between thefoam 84 and one of the two plate-like contacts 23, as a result of whichthe wick is coupled in terms of capillary action to the liquid material16. The foam 84 is held by a cartridge housing 85, together with whichthe foam forms an exchangeable cartridge 86. The cartridge 86 isinserted into a corresponding recess 87 in the housing 3. The recess 87is sealed in an airtight manner to the outside by a cover 88. The cover88 is fixed to the housing 3 by means of a snap connection 89. Thisfixing also causes the cover 88 to exert a compressive force on thecartridge 86 in the direction of the composite 22, 39. As FIG. 28 showsin more detail, the composite 22, 39 is mounted on an elevation 90 ofthe plate-like contact 23. The elevation 90 together with thecompressive force acting on the cartridge causes compression of the foam84—see compression stroke h. The compression has the effect that a smallquantity of the liquid material 16 is pressed out of the foam 84 in thecontact region with the composite, which quantity suffices to ensurecoupling in terms of capillary action between a newly inserted cartridge86 and the wick. The cartridge housing 85 is perforated on the sidefacing the cover 88. The ventilation holes 91 communicate with thechamber 21 via a cutout 92 in the cover 88 and thereby compensate forthe pressure between the liquid material 16 bound in the pores of thefoam 84 and the chamber 21. The foam 84 preferably consists of afine-pored polyether-polyurethane foam material which can beadditionally compressed. In prototypes, foam material compressed two tothree times and having the name “Jet 6” from the manufacturer FritzNauer AG, www.foampartner.com has been successfully used. The liquidstorage system just illustrated has the disadvantage that the cartridge86 can be removed from the inhalator component 2. This is, of course,associated with risks, for example the risk of the relatively smallcartridge 86 being swallowed by small children. The liquid storagesystem is therefore not suitable for storing drugs or/and poisons, forexample nicotine.

Further general parts of the inhalator according to the invention, whichparts are present in all of the exemplary embodiments, will be describedin more detail below: as FIGS. 6A-6C, FIG. 9 and FIG. 19 show, theplate-like contacts 23 of the exchangeable inhalator component 2protrude out of the outer surface of the housing 3 in the form of twoplug contacts 93. Over the course of the coupling of the inhalatorcomponent 2 to the inhalator part 1, the plug contacts 93 together withcorresponding spring contacts 94 form electric contacts via which theelectric energy for evaporating the liquid material 16 is supplied tothe heating element. The spring contacts 94 are part of the contactelements 20 and are connected to the latter, preferably by a weldedconnection—also see FIGS. 4-5. The contact elements 20 are preferablycomposed of a metallic contact material and can be manufactured, forexample, by Ami Doduco GmbH, www.amidoduco.com. In the event that thesame or similar material as for the heating element, for examplestainless steel, is used for the reasons already mentioned for theplate-like contacts 23, it is necessary, due to the inadequateconductivity of said material, to cover the plate-like contacts 23, atleast in the region of the plug contacts 93, for example galvanically,with a conductive layer of gold, silver, palladium or/and nickel, thussubstantially reducing the electric contact resistance. The contactelements 20 obtain the electric energy via two wires which connect thecontact elements 20 to the printed circuit board 11—see FIGS. 4-5. Thewires 95 are preferably fastened on both sides by means of soldering. Insummary, it should be pointed out once again that the contact elements20 carry out up to three different tasks: firstly, as just describedpreviously, they transmit the electric energy from the printed circuitboard 11 to the plate-like contacts 23. Secondly, they form laterallatching lugs 9 which interact with the snap-in hooks 8 of the housing3, thus bringing about snap connection between the inhalator component 2and the inhalator part 1. Thirdly, one of the two contact elements 20forms a stop for the pin 46, thus producing the ram-like operativeconnection for opening the liquid container 4. The latter task appearsonly in a variant embodiment of the inhalator and the liquid containersystem thereof.

For the positionally precise coupling of the inhalator component 2 tothe inhalator part 1, a positioning device is provided which consists ofa sintering projection 96 arranged on the support housing 10 and of acentering recess 97 which corresponds to said sintering projection andis arranged on the housing 3—see FIGS. 3A-3C, FIGS. 6A-6C, FIG. 10 andFIG. 12. The centering projection 96 has two venting holes 98 which ventthe centering recess 97 during the coupling.

FIGS. 29A and 29B show an exchangeable inhalator component 2 of aninhalator according to the invention, which inhalator component differsfrom the inhalator components previously illustrated by having twoplanar composites 22 a and 22 b arranged next to each other. The planarcomposites 22 a and 22 b can be constructed, for example, as alreadydescribed in detail in FIGS. 14-15. The planar composites 22 a and 22 band the heating resistors thereof are electrically connected to oneanother in series. The series connection causes the resulting heatingresistance to double given an unchanged composite span, if identicallysized individual resistances of the composites 22 a and 22 b are takenas a basis. The advantageous effects of said increase in resistance havealready been explained earlier. In principle, the heating resistance ofthe composite could also be increased by enlarging the composite span.However, this would have highly disadvantageous effects on theinfiltration duration which is the duration required by the liquidmaterial 16 in order to completely infiltrate the wick again followingevaporation. The infiltration duration would increase abruptly. If, byway of example, the composite specifications according to table 1 aretaken as the starting point, and two composites 22 a and 22 b having acomposite width of in each case 4 mm and an etching rate of 25% areconnected in series, this results in a heating element resistance ofapproximately 275 mOhm. At this resistance value, it is appropriate toreduce the composite span even further with regard to a shortinfiltration period, for example to 12 mm, as result of which theheating element resistance will drop to a value of approximately 235mOhm. The two composites 22 a and 22 b can optionally also havedifferent resistance values, which can be realized in an extremelysimple manner by different composite widths being assigned to the twocomposites. This enables the evaporation process to be spatially varied.Furthermore, the two composites 22 a and 22 b can optionally be fed bydifferent sources of liquid material. By means of the latter tworefinement options, it is possible still to have targeted influence onthe aerosol formation process and ultimately on the properties of thecondensation aerosol formed. For example, the evaporation process in thedistillation zone of a cigarette can thereby be approximately simulatedin space and time.

The composites 22 a and 22 b are mounted in turn with the end sectionsthereof on electrically conductive, plate-like contacts, and the heatingelements thereof are in contact connection electrically with thecontacts. In contrast to the exemplary embodiments described earlier,the plate-like contacts are split on one side into two contact parts 23a and 23 b which are insulated electrically from each other. The firstplanar composite 22 a is mounted with an end section on the contact part23 a, and the second planar composite 22 b is mounted with an endsection on the contact part 23 b. On the opposite side, the twocomposites 22 a and 22 b are mounted with the end sections thereof on acommon plate-like contact 23 c. The plate-like contact 23 c connects thetwo composites 22 a and 22 b electrically to each other. The plate-likecontact 23 c brings about the actual electric series connection whilethe electric energy is supplied to the composites 22 a and 22 b via thecontact parts 23 a and 23 b. The electric coupling to the reusableinhalator part 1 takes place again via the plug contacts 93, thearrangement of which is identical to the coupling scheme of thepreviously illustrated exemplary embodiments, cf. FIGS. 6A-6C, FIG. 9and FIG. 19. In order to be able to maintain said coupling scheme, inthe specific exemplary embodiment the contact part 23 a is configuredsuch that it extends transversely through the housing 3 to the oppositeside of the inhalator component 2 via a connecting web 110. As FIG. 29Ashows, the connecting web 110 runs below the slot-shaped channel 26.Instead of the connecting web 110, as an alternative a wire could alsoproduce the electric connection. Furthermore, it would alternativelyalso be possible to lead the two plug contacts 93 out of the housing onthe same housing side, with that side on which the contact parts 23 aand 23 b are also arranged obviously being appropriate here. Finally, itshould also be mentioned that the plate-like contacts or contact parts23 a, 23 b and 23 c can also be formed by printed circuit boards or byan individual common printed circuit board. Thick copper printed circuitboards having copper layer thicknesses in the range of 100-500 μm arepreferred because of better heat dissipation. Good heat dissipationshould be ensured especially in the region of the capillary gap 41 inorder to prevent boiling of the liquid material 16 in the capillary gap41.

The sensor 99, 100—see FIG. 8, FIG. 18 and FIGS. 21-22—forms asubstantial part of the inhalator according to the invention. The sensor99, 100 has the task of detecting the beginning of drawing orinhalation, whereupon the electric switching circuit 11 actives thesupply of electric energy to the heating element of the composite 22, 39and initiates the evaporation of the liquid material 16. At least twodifferent types of sensors can be used: in the exemplary embodimentaccording to FIG. 8, the sensor consists of a pressure sensor 99. Thepressure sensor 99 is adhesively bonded into the support housing 10, andthe electric connections or pins 101 thereof are soldered directly onthe printed circuit board 11. The pressure sensor 99 communicates withthe plenum chamber 27 via a bore 102 and measures or monitors thenegative pressure in the plenum chamber 27—see FIG. 18. An example of asuitable pressure sensor 99 is the CPCL04GC type with a measuring rangeof +/−10 mbar from the manufacturer Honeywell Inc., www.honeywell.com.The abovementioned sensor consists substantially of a zero-calibratedand temperature-compensated measuring bridge and can be connected to theprinted circuit board 11 as follows: the negative sensor output isgrounded via a high ohmic resistance having a defined resistancevalue—for example 2.2 MOhm, as a result of which the output signal ormeasuring signal of the pressure sensor 99 is slightly distorted, or inother words, worded, the offset of the measuring bridge is calibrated toa defined value. The distortion or the offset predetermines a switchingthreshold which corresponds to a certain pressure threshold value. Themeasuring signal prepared in this manner is connected across to theinput of a precision operation booster 103, which is connected in theform of a comparator—for example of the LTC1049CS8 type from themanufacturer Linear Technology Inc., www.linear.com. This connectionresults in an output signal which rapidly and exactly depicts thebeginning of drawing in digital form. The pressure sensor 99 is suitableespecially for use in drawing inhalators, if a flow throttle 28 isarranged upstream of the plenum chamber 27. In this case, a negativepressure typically lying within the range of 0-50 mbar with respect tothe surroundings occurs in the plenum chamber 27 over the course ofdrawing. The pressure profile is approximately in the shape of a bell.The beginning of drawing can be detected in a simple manner by, aspreviously described, predetermining a pressure threshold value which isconstantly compared with the actually measured value. The beginning ofdrawing can be defined as the first time the pressure threshold value isexceeded. Expediently, a value within the range of 0.2-5 mbar isselected for the pressure threshold value. If a lower pressure thresholdvalue is selected, the drawing identification responds more rapidly. Alower limit is defined by the specifications of the pressure sensor andoperation booster used in each case. If there is no flow throttle 28 inthe inhalator, ambient pressure virtually prevails in the plenum chamber27. The exemplary embodiment according to FIGS. 21-22 has theserequirements. The classic inhalator illustrated operates approximatelyunder atmospheric pressure conditions and permits direct inhalation intothe lungs in a single step. In this case, it is more expedient to detectthe beginning of inhalation by means of a flow sensor 100. In theexemplary embodiment according to FIGS. 21-22, the flow sensor 100 isarranged in the transverse channel 29, and the connections or pins 101of said flow sensor are again soldered directly on the printed circuitboard 11. A thermistor 100, preferably of the GRO15 type from themanufacturer Betatherm Corporation, www.betatherm.com, is suitable asthe flow sensor 100. The thermistor 100 is connected on the printedcircuit board 11 to a measuring bridge (not illustrated). Fortemperature compensation purposes, the measuring bridge contains asecond thermistor of identical type and is calibrated to a definedoffset threshold value by means of precision resistors. The outputsignal of the measuring bridge is then again connected across to theinput of an operation booster 103, which is connected in the form of acomparator. In the state of equilibrium, the two thermistors are at thesame temperature level—typically within the range of 80-200° C.,depending on the dissipated power. If a user then begins with theinhalation, air flows through the transverse channel 29. The air coolsthe thermistor 100, thus increasing the resistance thereof. The changein resistance is processed by the measuring bridge. At the moment atwhich the output signal of the measuring bridge passes through zero, thecomparator 103 tilts and emits a digital signal indicating the beginningof inhalation.

The signals output by the sensors 99, 100 and the connections thereofare preferably further processed in an integrated switching circuit104—see FIG. 8 and FIG. 21. The integrated switching circuit 104 mayalso be a microprocessor. The integrated switching circuit 104 processesa large part of all of the electric signals of the inhalator and carriesout the control operations essential for operating the inhalator. Thesecontrol operations will be explained in more detail below: a centralcontrol operation constitutes the supply of electric energy to theheating element of the composite 22, 39. The electric energy is suppliedby the energy store 12. On the basis of the current prior art,lithium-polymer and lithium-ion cells are particularly appropriate asenergy stores 12 owing to the high energy and power density thereof. Inthe event of metallic heating elements, even an individuallithium-polymer cell or lithium-ion cell with an idling or nominalvoltage of approximately 3.7 V suffices. The energy and power supply tothe heating element of the composite 22, 39 can be controlled in asimple manner by the battery voltage being chopped with a variable levelcontrol degree over the duration of the supply of energy, and theresultant useful voltage being applied to the heating element. Theresulting useful voltage is a square wave signal having a variable dutycycle. Apart from low voltage losses, the amplitude of the square wavesignal corresponds to the battery voltage. The actual choppingpreferably takes place by means of a power MOSFET 105, for example theIRF6635 type from the manufacturer International Rectifier, www.irf.com,which is suitable for switching very high currents with a minimumdrain-source forward resistance. In this case, the integrated switchingcircuit 104 controls the gate of the power MOSFET 105. A very simplecontrol strategy which has moreover also proven successful in prototypesaccording to the invention consists in dividing the duration of thesupply of energy into two periods—into a heating-up period and afollowing evaporation period. In the intermittent operation of theinhalator, synchronous with inhalation or drawing, the duration of thesupply of energy is oriented to the drawing or inhalation duration. Inthe case of drawing inhalators, for example, the starting point can bean average drawing duration of approximately 2.1 sec (+/−0.4 sec). Thesame value approximately also applies to cigarettes. If it is taken intoconsideration that, even after the supply of energy is switched off, acertain degree of reevaporation takes place because of the heat stillstored in the composite 22, 39, it appears to be expedient to select theduration of the supply of energy to be somewhat shorter, for example avalue within the range of 1.5-1.8 sec. In the case of classicinhalators, it may be advantageous within the context of a high degreeof drug absorption in the alveoli to reduce the duration of the supplyof energy even further. This is because drawing inhalators have theadvantage over classic inhalators that the drug is located as it were atthe very front of the air column inhaled into the lungs, as a result ofwhich the drug can more easily penetrate as far as the alveoli. Bycontrast, in classic inhalators, the drug passes directly into theinhaled air column. It should be taken into consideration in this casethat one end section of the inhaled air column serves only to fill the“functional dead space” (approx. 150-200 mL) of the respiratory system.Portions of drug in said dead space at any rate no longer reach thealveoli and are lost in this respect for a rapid, systemic action. If itis furthermore taken into consideration that the inhalation durationgreatly fluctuates individually, namely approximately between 1.5-3 sec,it appears to be expedient to select a value <1.5 sec for the durationof the supply of energy in classic inhalators. During the first of thetwo periods previously mentioned—the heating-up period—the composite 22,39 together with the liquid material 16 stored in the wick is heated upby the heating element. The evaporation of the liquid material 16 isinitiated only when the temperature of the composite 22, 39 hasapproximately reached the boiling range of the low-boiling fractions ofthe liquid material 16. The heating-up period should therefore be asshort as possible. It is obvious in this respect that the batteryvoltage should be passed on to the heating element in this periodunchopped or with a level control degree or duty cycle of 100%. Theduration of the heating-up period depends especially on thespecifications of the composite 22, 39 and on the quantity andcomposition of the liquid material 16 to be evaporated and should be asfar as possible <0.5 sec. In the subsequent second period—theevaporation period—the level control degree is substantially withdrawn,and the actual evaporation of the liquid material 16 takes place. Insaid second period, the supplied energy is used primarily to evaporatethe liquid material 16 and secondarily to cover energy losses. By meansof appropriate selection of the level control degree, the evaporativecapacity and therefore the quantity of liquid material 16 evaporated perdrawing or inhalation can be controlled within certain limits. An upperlimit is imposed by the occurrence of a boiling crisis and by localdrying out and overheating of the wick. In contrast, thermaldecomposition of the liquid material 16 can be counteracted bywithdrawing or throttling the level control degree.

The control strategy just described can be expanded and refinedarbitrarily: for example, it may be expedient also to take the state ofthe battery into consideration in the control strategy, since thebattery voltage significantly drops with increasing discharge andincreasing age of the battery, especially under load. This effect can becountered by an increase in the level control degree. In order to beable to carry out this correction even in the heating-up period, it isexpedient to drive the battery voltage of a new, charged battery only at80%, for example, rather than at 100% as proposed earlier, and thereforethere is still a sufficient amount of room for adaptation.

In addition, the control of the supply of energy to the heating elementof the composite 22, 39 requires various auxiliary operations: forexample, provision has to be made for the supply of energy not to beimmediately activated again after the end of an evaporation cycle. Onthe contrary, a waiting time should be maintained leaving sufficienttime for the liquid material 16 to completely infiltrate the wick again.The minimum waiting time required depends on the particularspecifications of the composite and on the viscosity of the liquidmaterial. In prototypes, it could be shown and calculations couldconfirm that, given an appropriate configuration, complete infiltrationof the wick can be obtained in less than 10 sec. A compulsory waitingtime of this order of magnitude should be tolerated by most users,especially if it is taken into consideration that the interval betweentwo drawings is on average 25 sec in the case of a cigarette. A waitingtime of this type should also be maintained after coupling a newinhalator component 2 to the inhalator part 1. Another auxiliaryoperation involves the supply of energy to the heating element beingbroken off immediately if the user prematurely breaks off the drawing orinhalation. This prevents vapor from unnecessarily being formed in thechamber 21.

A further control operation of the integrated switching circuit 104relates to the user interface, i.e. communication with the user. Thesensor 99, 100 for identifying the beginning of drawing or inhalationconstitutes an input interface and is indispensable as such.Furthermore, in a very simple refinement of the user interface, nofurther input interface is provided, not even an on-off switch, andtherefore the use of the inhalator turns out to be extremelyuncomplicated. Of course, the lack of an on-off switch presupposes thatthe electric switching circuit 11 requires an appropriately small amountof current, which should be taken into consideration when preparing thecircuit diagram. For example provision may be made for the switchingcircuit 11 to switch into a particularly energy-saving sleep mode if aninhalator component 2 is not coupled to the inhalator part 1. As outputinterfaces, use may be made, for example, of two light-emitting diodes106, the first of which shows the charging state of the battery 12, andthe second of which signals the approaching changeover interval of theinhalator component 2. The changeover interval of the inhalatorcomponent 2 can be monitored by a counter which counts the number ofdrawings or inhalations. During the interchanging of the inhalatorcomponent 2, the counter is reset to zero, with use being made of thefact that the heating element resistance is infinitely large for amoment. In a somewhat more complicated refinement, instead of thelight-emitting diodes 106, a display (not illustrated) can be integratedin the switching circuit cover 7. In addition to the battery chargingstate and the approaching changing over of the inhalator component 2,the display can also indicate further operating states and information,for example the drug dose supplied as a whole for a certain period oftime. In the case of nicotine, it makes it possible in a highlyobjective manner to ascertain the degree of nicotine dependency of theuser and, over the course of a gradual withdrawal, to ascertain thesuccess actually obtained. Finally, the display can assist the user inthe form of a user guide for operating the inhalator. It is alsopossible to provide as an output interface an acoustic, vibratory or/andoptical alarm which assists the user in supplying the particular drug atthe correct time and in the required dose. Finally, a data interface mayalso be provided, for example in the form of a USB or Bluetoothinterface, via which in particular firmware and software updates aremerged, diagnosis functions are carried out and information, inparticular relating to the drug dose administered, can be read. By meansof the latter function, a doctor carrying out the treatment can exactlyand objectively record and evaluate the drug dose supplied over aprolonged period and the temporal profile of said dose, and cancoordinate his medicinal treatment thereto.

A further control operation which can optionally be provided relates tothe identification of the inhalator component 2 used, the identificationof the user and, associated therewith, the ascertaining of misuse of theinhalator. The inhalator component 2 together with the type of compositeand liquid material 16 contained therein can be identified in a simplemanner by measuring the heating element resistance. However, this methodhas certain limits because each drug preparation has to be assigned acertain type of composite with a defined heating element resistance. Asomewhat more complicated method involves arranging an identificationchip (not illustrated) in the inhalator component 2, said identificationchip unambiguously identifying the inhalator component 2. With the aidof a chip of this type, it is possible to unambiguously identify eachindividual inhalator component 2 produced and sold. The chip ispreferably arranged on one of the two plate-like contacts 23, with itbeing particularly favorable if the plate-like contact 23 is formed by aprinted circuit board. The information stored in the chip is read by anintegrated switching circuit 104 which, in this case, preferablyconsists of a microprocessor. On the basis of the information read, themicroprocessor 104 selects the operating parameters suitable for theinhalator component 2 used. Furthermore, after reaching the changeoverinterval, the microprocessor 104 can block the particular inhalatorcomponent 2 or render the latter unusable by certain means such that nofurther drawings or inhalations can be carried out with said inhalatorcomponent 2. This measure serves especially to avoid misuse of theinhalator component 2. Misuse of this type would involve, for example, auser attempting to continue to use the inhalator component 2 beyond thechangeover interval by, for example, forcibly opening the liquidcontainer 4 and refilling the latter with liquid material 16 himself Inthe case of nicotine, the lethal dose (LD50) is circa 0.5-1.0 mg/kg ofbody weight. It can be imagined how hazardous such a misuse would be forthe user and his environment. The risk of misuse of this type and theenvironmental hazard due to used inhalator components 2 which have beenthrown away can be further reduced by the inhalator component 2 beingsold under the deposit system. The identification of the user serves toprevent the inhalator being used by an unauthorized third party andthereby also prevents theft. The user can be identified, for example,via a touch display by inputting a code, or biometrically by means of afingerprint.

A further control operation which can be carried out by the integratedswitching circuit 104 relates to the cell and charging management of thebattery 12. Since switching circuits which are already integrated areavailable commercially for this purpose, said control operation mayalternatively also take place in a separate integrated switchingcircuit. The charging current is supplied via the charging plug 107which is arranged on that end side of the inhalator part 1 which facesaway from the mouthpiece 5—see FIGS. 3A-3C and FIG. 8. The charging plug107 may at the same time be a diagnostic plug via which the electricswitching circuit 11 and the heating element resistance of the composite22, 39 can be checked by means of an external analyzer and possibleerrors can be detected.

The previously described control operations can be converted into acircuit diagram by a person skilled in the art in this field using knownmethods, and will therefore not be described in more detail in thiscontext.

Finally, the functioning and operation of the inhalator according to theinvention will be explained once again in summary: the user makes a newinhalator component 2 ready for use by coupling the latter to thereusable inhalator part 1 via the snap connection 8, 9. In the exemplaryembodiment according to FIGS. 6A-6C, the liquid container 4 is openedsynchronously to the coupling to the inhalator part 1 by means of thepin 46 in interaction with the contact element (see FIG. 19). Bycontrast, in the exemplary embodiment according to FIG. 24a and FIG. 24b, the liquid container 4 is opened by the user displacing the liquidcontainer 4 into the housing 3 (see arrow direction). In both cases, oneend of the capillary gap 41, which end is designed as an extension 44(FIG. 19) or as a first spike 81 (FIG. 25), is wetted with the liquidmaterial 16. The capillary gap 41 exerts a capillary force on thewetting liquid material 16, said capillary force causing the capillarygap 41 to be rapidly flooded. The liquid material 16 reaches thecomposite 22, 39 (see FIG. 11). The composite 22, 39 consists of a wickand an electric heating element. The capillary forces in the wick causethe latter to be infiltrated likewise rapidly by the liquid material 16.At the same time, the buffer store 53 consisting of capillaries 54 isalso flooded by the liquid material 16. The buffer store 53 permitsposition-independent operation of the inhalator. The duration betweenthe opening of the liquid container 4 and complete infiltration of thewick corresponds to a compulsory waiting time for the user and, given anappropriate configuration, is at any rate less than 10 sec. Theinhalator is now ready for operation. In the case of a drawing inhalatoraccording to the invention (FIGS. 9-10), the user carries out drawingvia the mouthpiece 5 in a similar manner as for a cigarette and, in thecase of a classic inhalator according to the invention (FIGS. 21-22),the user carries out direct inhalation into the lungs. The sensor 99,100 (FIG. 8 and FIG. 21) detects the beginning of drawing or inhalationand leads to the integrated switching circuit 104 supplying the heatingelement of the composite 22, 39 with electric energy in accordance witha predetermined control strategy. This results in the composite 22, 39heating up rapidly and evaporating the liquid material 16 in the wick.The vapor formed leaves the composite 22, 39 via the wick surface, whichis exposed over wide regions of the composite, and mixes in the chamber21 with the air flowing into the chamber 21 through the air inletopening 26. By mixing with the air, the vapor cools and forms acondensation aerosol (FIGS. 9-10 and FIGS. 21-22). Excess condensatewhich does not contribute to forming the condensation aerosol orvapor-air mixture is sucked up and bound by sponges 57 arranged in thechamber 21. In the exemplary embodiment according to FIGS. 9-10 (drawinginhalator), the vapor-air mixture or/and condensation aerosol formed, inorder to improve the organoleptic properties thereof, also flows throughthe filling material 61 before finally entering the user's mouth cavityvia the mouthpiece channel 66. In the exemplary embodiment according toFIGS. 21-22 (classic inhalator), the vapor-air mixture or/andcondensation aerosol formed emerges out of the chamber 21 through themouth opening 71 formed by the guide vanes 69 and is combined with thebypass air flowing through the bypass openings 68 in order finally,after flowing through a flow homogenizer 72 optionally arranged in themouthpiece channel 66, likewise to enter the user's mouth cavity. Aftera waiting time of a few seconds, the liquid material 16 has againcompletely infiltrated the wick of the composite 22, 39, and theinhalator is ready for further inhalation. If the liquid container 4contains, for example, 2.5 mL of effectively useable liquid material 16,and if the liquid material contains nicotine as the drug in aconcentration of typically 1.5% by vol., then with an inhalatorcomponent of this type up to 380 drawings or inhalations can be carriedout if 100 μg of nicotine is evaporated per inhalation. 380 drawingscorresponds approximately to 38 cigarettes. If only 50 μg of nicotine isevaporated per inhalation, then the range extends to 760 inhalations,which value approximately corresponds to four packs of cigarettes.

Finally, with reference to the drug nicotine, an exemplary preparationof the liquid material 16 should be disclosed, which preparation isevaporated in prototypes according to the invention configured asdrawing inhalators. With regard to the pharmacological, pharmacokineticand organoleptic effects, the condensation aerosol formed andadministered in this case came very close to the smoke of a conventionalcigarette. All of the listed contents are also found again in cigarettesmoke.

TABLE 2 Exemplary drug preparation on the basis of nicotine SubstanceCAS number % by mass Ethanol 64-7-5 68.80 Water 7732-18-5 16.50 Glycerol56-81-5 9.10 Nicotine 54-11-5 1.80 Lactic acid 50-21-5 0.23 Succinicacid 110-15-6 0.28 Levulinic acid 123-76-2 0.46 Benzoic acid 65-85-00.08 Phenyl acetic acid 103-82-2 0.08 Acetic acid 64-19-7 1.67 Formicacid 64-18-6 0.53 Propionic acid 79-09-4 0.27 Solanone 1937-54-8 0.05Tobacco aroma oils *) 0.15 Ambroxide 6790-58-5 optional Menthol2216-51-5 optional Totals: 100.00 *) Tobacco aroma oils obtained bymeans of supercritical CO.sub.2 extraction; for example tobacco extractsfrom Pro-Chem Specialty Limited, Hong Kong, www.pro-chem-specialty.com,for example product No. SF8010, SF8011 or SF208118; or tobacco aromaoils produced according to patent publication numbers DE19654945A1,DE19630619A1, DE3218760A1 or DE3148335A1 (Adam Muller et al.); aprerequisite for the use of tobacco aroma oils of this type in thenicotine solution is that these oils are as free as possible fromtobacco-specific nitrosamines (TSNA).

For the sake of completeness, it should furthermore also be noted thatit is possible to integrate additional functions in the inhalatoraccording to the invention, said functions going beyond the actual taskof the inhalator and expanding the inhalator into a multifunctionalappliance or hybrid appliance. Functions of this type may include, forexample: a clock, mobile data store, player functions (includingdictation function), PDA functions, navigation aid (GPS), cell telephonyand photography.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a wick with a capillarystructure, wherein the wick forms a composite with the heating elementand automatically resupplies the heating element with the liquidmaterial following evaporation, wherein the composite has a thickness ofless than 0.6 millimeters (mm). In another embodiment, the composite hasa thickness of less than 0.3 mm.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a wick with a capillarystructure, wherein the wick forms a composite with the heating elementand automatically resupplies the heating element with the liquidmaterial following evaporation, wherein the composite has a porosity ofgreater than 50%. In another embodiment, the composite has a porosity ofgreater than 70%. In yet another embodiment, the composite has aporosity of greater than 90%.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a wick with a capillarystructure, wherein the wick forms a composite with the heating elementand automatically resupplies the heating element with the liquidmaterial following evaporation, wherein the composite has an open-poredsintered structure. In other embodiments, the open-pored sinteredstructure comprises a fibrous sintered structure, a granular sinteredstructure, or a mesh. The mesh can comprise stainless steel.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; a wick with a capillary structure,wherein the wick forms a composite with the heating element andautomatically resupplies the heating element with the liquid materialfollowing evaporation; and a plurality of electrical contacts eachconnected with the composite at a laser weld.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; a wick with a capillary structure,wherein the wick forms a composite with the heating element andautomatically resupplies the heating element with the liquid materialfollowing evaporation; and a buffer store configured to receive liquidmaterial and to dispense the received liquid material to the wick whenthe liquid material is needed and irrespective of a position of theinhalator component. In one embodiment, the buffer store is configuredto receive the liquid material from a capillary gap and dispense theliquid material via the capillary gap. In one embodiment, the capillarygap is arranged at an end of the composite.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a wick with a capillarystructure, wherein the wick forms a composite with the heating elementand automatically resupplies the heating element with the liquidmaterial following evaporation, and wherein a surface of the compositehas been subjected to surface activation.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a flow sensor comprising afirst thermistor to detect a beginning of inhalation. In one embodiment,the inhalator component further comprises a second thermistor. In oneembodiment, the flow sensor is arranged in an air flow path of theinhalation.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and wherein a supply of energy fromthe inhalator device to the heating element is divided into at least twoperiods, a heating up period and an evaporation period, the evaporationperiod following the heating up period. In one embodiment, during theevaporation period a modulated voltage is applied to the heatingelement. In one embodiment, during the heating up period an unmodulatedvoltage is applied to the heating element.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; and anelectric heating element for evaporating a portion of a liquid material,wherein a vapor that is formed is mixed in the chamber with the airsupplied through the air admission opening to form the at least one ofthe vapor air mixture or condensation aerosol, wherein a supply ofenergy from the inhalator device to the heating element is for a timeperiod less than a period of activation of the inhalator device. In oneembodiment, the period of activation is a period of inhalation. In oneembodiment, the period of activation is a period of activation of aswitch/button by a user.

In an embodiment, inhalator component for an inhalator device, for theintermittent formation, synchronous with inhalation or drawing, of atleast one of a vapor air mixture or a condensation aerosol, comprises ahousing; a chamber arranged in the housing; an air admission opening forthe supply of air from the surroundings to the chamber; and an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol, wherein a supply of energy from theinhalator device to the heating element is modulated to prevent thermaldecomposition of the liquid material.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; and anelectric heating element for evaporating a portion of a liquid material,wherein a vapor that is formed is mixed in the chamber with the airsupplied through the air admission opening to form the at least one ofthe vapor air mixture or condensation aerosol, wherein a supply ofenergy from the inhalator device to the heating element is modulated tocontrol at least one characteristic of the at least one of the vapor airmixture or condensation aerosol. In one embodiment, the at least onecharacteristic is a quantity of liquid material evaporated perinhalation. In one embodiment, the supply of energy to the heatingelement is modulated during inhalation. In one embodiment, the supply ofenergy to the heating element is modulated between inhalations. In oneembodiment, the supply of energy is modulated according to a rate ofinhalation. In one embodiment, the inhalator component further comprisesa user interface, wherein the supply of energy is modulated according toinput received via the user interface.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol; and a cooler through which the atleast one of the vapor air mixture or condensation aerosol passes. Inone embodiment, the cooler provides aromatization of the at least one ofthe vapor air mixture or condensation aerosol. In one embodiment, thecooler comprises a tobacco filling. In one embodiment, the cooler isformed by the tobacco filling. In one embodiment, the cooler comprises apore body. In one embodiment, the pore body comprises at least one of awide-pored material, a coarse-pored porous filling material, a nonwovenfiber material or a regenerator material. In one embodiment, the porebody comprises a wide-pored material, and wherein the wide-poredmaterial comprises an open-cell foam material. In one embodiment, thepore body comprises a nonwoven fiber material, and wherein the nonwovenfiber material comprises a synthetic nonwoven fiber material. In oneembodiment, the synthetic nonwoven fiber material comprises polyolefinfibers or polyester fibers. In one embodiment, the pore body comprises aregenerator material, and wherein the regenerator material comprises atleast one of a metal wool, a metal chip, a metal mesh, a wire knit, ametal nonwoven, an open-cell metal foam, a metallic granular material,or a ceramic granular material.

In an embodiment, an inhalator component for an inhalator device, forthe intermittent formation, synchronous with inhalation or drawing, ofat least one of a vapor air mixture or a condensation aerosol, comprisesa housing; a chamber arranged in the housing; an air admission openingfor the supply of air from the surroundings to the chamber; an electricheating element for evaporating a portion of a liquid material, whereinthe electric heating element comprises an induction heating element, andwherein a vapor that is formed is mixed in the chamber with the airsupplied through the air admission opening to form the at least one ofthe vapor air mixture or condensation aerosol; and a wick with acapillary structure, wherein the wick forms a composite with theelectric heating element and automatically resupplies the electricheating element with the liquid material following evaporation.

LIST OF REFERENCE NUMBERS

1 Inhalator part

2 Inhalator component

3 Housing

4 Liquid container

5 Mouthpiece

6 Battery cover

7 Switching circuit cover

8 Snap-in hook

9 Latching lug

10 Support housing

11 Electric switching circuit, printed circuit board

12 Energy store; battery

13 Partition

14 Flat contact

15 Window

16 Liquid material; drug preparation

17 Filling hole

18 Openable closure

19 Closure cover

20 Contact element

21 Chamber

22 Planar composite

23 Plate-like contact

24 First side of the planar composite

25 Second side of the planar composite

26 Air admission opening; slot-shaped channel

27 Plenum chamber

28 Flow throttle

29 Transverse channel

30 Feeding opening

31 Film; metal foil

32 Fabric; metal wire mesh

33 Open-pored fiber structure; nonwoven fabric

34 Open-pored sintered structure; granular, fibrous or flocculentsintered composite

35 Channel; artery

36 Hole

37 Open-pored foam

38 Support layer

39 Linear composite

40 Ram

41 Capillary gap

42 Upper part

43 Plate

44 Extension

45 Reservoir

46 Pin

47 First end

48 Second end

49 Material weakening

50 Hinge

51 Cross-sectional expansion

52 Ventilation duct

53 Buffer store

54 Capillary; slot

55 Opening

56 Ventilation gap

57 Open-pored, absorbent body; sponge

58 Flow duct

59 Wall section

60 Gap

61 Cooler; filling material; tobacco filling

62 Filling space

63 Perforated wall

64 First wire mesh

65 Second wire mesh

66 Mouthpiece channel

67 Collecting chamber

68 Bypass opening

69 Guide vane

70 Guide van tip

71 Mouth opening

72 Flow homogenizer

73 Blocking device which cannot be unlocked; projection

74 Catch

75 Groove

76 Venting opening

77 Venting duct

78 First opening

79 Second opening

80 Film seals

81 First spike

82 Second spike

83 Microweb

84 Liquid store; open-pored foam

85 Cartridge housing

86 Cartridge

87 Recess

88 Cover

89 Snap connection

90 Elevation

91 Ventilation hole

92 Cutout

93 Plug contact

94 Spring contact

95 Wire

96 Centering projection

97 Centering recess

98 Venting hole

99 Pressure sensor

100 Flow sensor, thermistor

101 Electric connection; pin

102 Bore

103 Operation booster; comparator

104 Integrated switching circuit; microprocessor

105 Power MOSFET

106 Light-emitting diode

107 Charging plug

108 Recess

109 Small locking plate

110 Connecting web

1. (canceled)
 2. A liquid material comprising: nicotine; glycerol andone or more acids selected from the group consisting of lactic,succinic, levulinic, benzoic, phenyl acetic, acetic, formic, andpropionic acid.
 3. The liquid material of claim 2, wherein the acid islactic acid.
 4. The liquid material of claim 2, wherein the acid issuccinic acid.
 5. The liquid material of claim 2, wherein the acid islevulinic acid.
 6. The liquid material of claim 2, wherein the acid isbenzoic acid. (New) The liquid material of claim 2, wherein the acid isphenyl acetic acid.
 8. The liquid material of claim 2, wherein the acidis acetic acid.
 9. The liquid material of claim 2, wherein the acid isformic acid.
 10. The liquid material of claim 2, wherein the acid ispropionic acid.
 11. The liquid material of claim 2, wherein the acidincludes both levulinic acid and benzoic acid.
 12. The liquid materialof claim 2, further comprising water.
 13. The liquid material of claim2, further comprising one or more aroma substances.
 14. The liquidmaterial of claim 13, wherein the one or more aroma substances areselected from the group consisting of tobacco extracts, tobacco aromaoils, menthol, coffee extracts, tobacco smoke condensates, andcombinations thereof.
 15. An inhaler component comprising: a housing, aliquid container containing a liquid material according to claim 1, theliquid material configured for evaporation within the inhaler componentto form an inhalable vapor-air mixture and/or condensation aerosol, anda mouthpiece for delivery of the inhalable vapor-air mixture and/orcondensation aerosol to a user.
 16. The inhaler component of claim 15,further comprising a heating element for evaporating a portion of theliquid material, and a wick supplying liquid material to the heatingelement.
 17. The inhaler component of claim 16, wherein aerosolparticles produced by condensation therein have a mass medianaerodynamic diameter (IVIMAD) of smaller than 2 μm.
 18. An inhalercomprising the inhaler component of claim 14 detachably coupled to asecond inhaler component comprising an energy store and an electricswitching circuit.
 19. An inhalator component for an inhalator device,for the intermittent formation, synchronous with inhalation or drawing,of at least one of a vapor air mixture or a condensation aerosol,comprising: a housing; a liquid store comprising nicotine and benzoicacid; a chamber arranged in the housing; an air admission opening forthe supply of air from the surroundings to the chamber; and an electricheating element for evaporating a portion of a liquid material, whereina vapor that is formed is mixed in the chamber with the air suppliedthrough the air admission opening to form the at least one of the vaporair mixture or condensation aerosol.
 20. The inhalator component ofclaim 19, wherein the liquid store further comprises glycerol.
 21. Theinhalator component of claim 19, further comprising one or moreflavorants, such as menthol.
 22. The inhalator component of claim 19,wherein the liquid store comprises one or more further acids selectedfrom the group consisting of lactic, succinic, levulinic, phenyl acetic,acetic, formic, and propionic acid.